Method and apparatus for magnetic resonance imaging of arteries using a magnetic resonance contrast agent

ABSTRACT

The present invention is a technique and apparatus for providing preferential enhancement of an artery of interest relative to adjacent veins and background tissue by correlating the collection of a predetermined portion of data of a magnetic resonance contrast image during the arterial phase of the magnetic resonance contrast enhancement. The arterial phase of the contrast enhancement may be described as a period of a maximum, substantially elevated, or elevated contrast concentration in the artery of interest relative to adjacent veins. The present invention includes a detection system for monitoring and detecting the arrival of the contrast agent in the artery and tissues of interest. When the concentration of contrast agent in the artery of the region of interest is maximum, substantially elevated or elevated (e.g., about 20-50% greater than the response of the region of interest to a series of magnetic resonance pulses before administration of a magnetic resonance contrast agent), a predetermined portion of the magnetic resonance image data (e.g., data which is representative of the center of k-space) may be acquired. Thus, the present invention facilitates synchronization between collecting the central portion of k-space image data with the arterial phase of contrast enhancement. The center of k-space corresponds to the lowest spatial frequency data which dominates image contrast.

This application is a continuation of application Ser. No. 08/777,347,filed Dec. 27, 1996, now U.S. Pat. No. 5,792,056, which is acontinuation of application Ser. No. 08/580,195, filed Dec. 28, 1995,now U.S. Pat. No. 5,590,654, which is a continuation-in-part ofApplication Ser. No. 08/071,970, filed on Jun. 7, 1993, now U.S. Pat.No. 5,417,213, application Ser. No. 08/378,384, filed Jan. 25, 1995 nowU.S. Pat. No. 5,553,619, and application Ser. No. 08/420,815, filed Apr.12, 1995 now U.S. Pat. No. 5,579,767.

BACKGROUND OF THE INVENTION

This invention relates to a method of, and apparatus for use in,magnetic resonance imaging; and more particularly, to contrast agentenhanced magnetic resonance angiography for examining, detecting,diagnosing, and treating arterial diseases and injuries, includingdefining anatomic features relevant to performing aorta and aorticsurgery for aneurysmal disease.

Arterial diseases and injuries are common and often have severeconsequences including death. Imaging arteries serves to detect andcharacterize arterial disease before these consequences occur as well asdefining anatomic features to assist in performing surgery foraneurysmal disease.

A conventional method of arterial imaging includes inserting a catheterinto the artery of interest (the artery under study) and injectingradiographic contrast, for example, an iodinated contrast, while takingradiographs of the artery. Radiographs are commonly referred to asX-rays. In this technique, the contrast remains in the arteries for afew seconds during which the arteries appear distinct from both theveins and background tissue in the radiographs.

Although a catheter-based contrast arteriography technique generallyprovides high quality arterial images, there is a risk of arterialinjury or damage by the catheter and its insertion. There may bethrombosis, dissection, embolization, perforation or other injury to theartery itself. Furthermore, such a technique may result in a stroke,loss of a limb, infarction or other injury to the tissue supplied by theartery. In addition, hemorrhage at the catheter insertion or perforationsites may require blood transfusions. Moreover, kidney failure and braininjury may result from the toxic effects of the X-ray contrast.

More recent techniques of arterial imaging are based upon detecting themotion of the blood within the arteries and/or veins. These techniquesinvolve employing magnetic resonance imaging (MRI) to image moving blooddistinct from stationary background tissues. (See, e.g., Potchen, etal., eds., “Magnetic Resonance Angiography/Concepts and Applications”,Mosby, St. Louis, 1993; the text of which is incorporated herein byreference). Such techniques do not necessitate catheter insertion intothe artery. These techniques are commonly known as 2D time-of-flight, 3Dtime-of-flight, MOTSA, magnitude contrast, phase contrast, and spin echoblack blood imaging.

With pre-saturation pulses it is possible to primarily image bloodflowing in one direction. Since arteries and veins generally flow inopposite directions, these pre-saturation pulses allow preferentialvisualization of the arteries or the veins. Because these techniquesdepend upon blood motion, the images are degraded in patients who havearterial diseases which decrease or disturb normal blood flow. Suchtypes of arterial diseases that decrease or disturb normal blood flowinclude aneurysms, arterial stenoses, arterial occlusions, low cardiacoutput and others. The resulting lack of normal blood flow isparticularly problematic because it is those patients with disturbedblood flow in whom it is most important to acquire good quality arterialimages.

A related MRI technique relies on differences in the proton relaxationproperties between blood and background tissues. (See, e.g., Marchal, etal., in Potchen, et al., eds., supra, pp. 305-322). This technique doesnot depend upon steady blood in-flow. Instead, this MRI techniqueinvolves directly imaging the arteries after administering aparamagnetic contrast agent. Here, after administering the contrastagent, it is possible to image arteries directly based upon the bloodrelaxation properties. This technique overcomes many of the flow relatedproblems associated with MRI techniques which depend upon blood motion.

Several experts have performed magnetic resonance arterial imaging usingintravenous injection of gadolinium chelates (paramagnetic contrastagents). These experts have reported their results and conclusions. Inshort, these results have been disappointing and, as a result, the useof gadolinium for imaging arteries has not been adopted or embraced as aviable arterial imaging technique. The images using this technique aredifficult to interpret because the gadolinium tends to enhance both thearteries and the veins. Since the arteries and veins are closelyintertwined, it is extremely difficult to adequately evaluate thearteries when the veins are visible. Further, the difficulty ininterpretation is exacerbated as a result of contrast leakage into thebackground tissues.

However, MRI has evolved over the past decade to become an acceptedtechnique to image the abdominal aorta and abdominal aortic aneurysms.Advances in magnetic resonance imaging for vascular imaging, known asmagnetic resonance angiography, have enabled the additional evaluationof aortic branch vessels. However, limitations in magnetic resonanceangiography imaging of the slow, swirling flow within aneurysms,turbulent flow in stenoses, and tortuous iliac arteries have limited theusefulness of these general studies in providing detailed informationnecessary for preoperative planning. In spite of these limitations,recent developments in gadolinium-enhanced magnetic resonanceangiography have overcome several of the imaging problems. (See, e.g.,Debatin et al., “Renal magnetic resonance angiography in thepreoperative detection of supernumerary renal arteries in potentialkidney donors”, Invest. Radiol. 1993;28:882-889; Prince et al., “Dynamicgadolinium-enhanced three-dimensional abdominal MR arteriography”, JMRI1993;3:877-881; and Prince, “Gadolinium-Enhanced MR Aortography”,Radiology 1994;191(1):155-64).

There exists a need for an improved method of magnetic resonanceangiography which provides an image of the arteries distinct from theveins and which overcomes the limitations of other techniques. Further,there exists a need for an apparatus which facilitates providing animage of the arteries distinct from the veins and which may beimplemented in overcoming the limitations of other techniques.

In addition, there exists a need for contrast (e.g., gadolinium)enhanced magnetic resonance angiography of abdominal aortic aneurysms toprovide essential and accurate anatomic information for aorticreconstructive surgery devoid of contrast-related renal toxicity orcatheterization-related complications attending conventionalarteriography.

SUMMARY OF THE INVENTION

In one principal aspect, the present invention is a method of imaging anartery of a patient using magnetic resonance imaging. The methodincludes the steps of detecting an elevated concentration of magneticresonance contrast agent in the artery and imaging at least a portion ofthe artery including collecting image data which is representative ofthe center of k-space after detecting the elevated concentration ofmagnetic resonance contrast agent in the artery.

In one embodiment of this aspect of the invention, image data which isrepresentative of the center of k-space may be collected when aconcentration of the contrast agent in the artery is substantiallyhigher than a concentration of the contrast agent in veins adjacent tothe artery. In another embodiment, this image data may be collected whenthe concentration of the contrast agent in the artery is greater than apredetermined concentration. In yet another embodiment, image data whichis representative of the center of k-space may be collectedsubstantially at the beginning of an imaging sequence.

The step of detecting an elevated concentration of magnetic resonancecontrast agent in the artery may include measuring a base line signalwhich is representative of a response of the artery to at least onemagnetic resonance radio frequency pulse prior to administering themagnetic resonance contrast agent to the patient.

In one embodiment, the artery may be monitored after administering thecontrast agent to the patient to detect the arrival of the contrastagent in the artery. The arrival of the contrast may be indicated bydetecting a change in the response of the artery to at least onemagnetic resonance radio frequency pulse. This change in the responsemay be a change in a maximum amplitude of a responsive RF signal or achange in the shape of an envelope of a responsive RF signal.

In another embodiment, image data which is representative of the centerof k-space is collected substantially at the beginning of an imagingsequence and while the concentration of the contrast agent in the arteryis substantially elevated.

In another principal aspect, the present invention is a method ofimaging an artery in a region of interest of a patient using magneticresonance imaging, comprising the steps of detecting a predeterminedconcentration of magnetic resonance contrast agent in the artery; andimaging at least a portion of the artery including collecting image datawhich is representative of the center of k-space after detecting thepredetermined concentration of the contrast agent in the artery andwhile the concentration in the artery is higher than a concentration ofthe contrast agent in veins adjacent to the artery.

In one embodiment of this aspect of the invention, the technique detectsthe arrival of the contrast in the artery. In this embodiment, imagedata which is representative of the center of k-space may be collectedsubstantially at the beginning of a 3D imaging sequence.

In another embodiment, image data which is representative of the centerof k-space is collected while the concentration in the artery issubstantially higher than a concentration of the contrast agent in veinsadjacent to the artery. In this embodiment, the step of detectingmagnetic resonance contrast agent in the artery includes detecting asubstantially elevated concentration of magnetic resonance contrastagent in the artery and the step of imaging at least a portion of theartery includes collecting image data which is representative of thecenter of k-space after detecting the substantially elevatedconcentration of magnetic resonance contrast agent in the artery.

In one embodiment, the magnetic resonance contrast agent is administeredto the patient by bolus type injection. Under this circumstance, imagedata which is representative of the center of k-space is collectedsubstantially at the beginning of a 3D imaging sequence.

In yet another principal aspect, the present invention is an apparatusfor imaging an artery in a region of interest of a patient usingmagnetic resonance imaging. The apparatus includes detecting means fordetecting a predetermined concentration of magnetic resonance contrastagent in the artery and, in response thereto, for generating an imaginginitiation signal. The apparatus also includes imaging means, coupled tothe detecting means, for collecting image data which is representativeof the center of k-space in response to the imaging initiation signal.

In one embodiment of this aspect of the invention, the imaging meanscollects the image data which is representative of the center of k-spacesubstantially at the beginning of a 3D imaging sequence. In anotherembodiment, the detecting means generates the imaging initiation signalwhen the concentration of the contrast agent in the artery issubstantially elevated.

Finally, in another principal aspect, the present invention is anapparatus for imaging an artery of a patient using magnetic resonanceimaging and a magnetic resonance imaging contrast agent, comprising,detecting means for generating an imaging initiation signal in responseto detecting the magnetic resonance imaging contrast agent in theartery; and imaging means, coupled to the detecting means, forcollecting image data which is representative of the center of k-spacein response to the imaging initiation signal.

The imaging means may collect image data which is representative of aperiphery of k-space after collecting image data which is representativeof the center of k-space.

The present invention overcomes the limitations of other techniques byinjecting magnetic resonance contrast agents and collecting image datain such a manner that the contrast level in the arteries is higher thanthat in surrounding veins and background tissue during collection ofimage data, including data which is representative of the center ofk-space.

A high level of arterial contrast also permits directly imaging thearterial lumen, analogous to conventional arteriography. In short, thepresent invention is, in comparison or relative to other techniques, amethod of magnetic resonance angiography which combines several of theadvantages of catheter-based contrast arteriography with the advantagesof magnetic resonance imaging while substantially eliminating thedisadvantages of each.

BRIEF DESCRIPTION OF THE DRAWINGS

In the course of the detailed description of preferred embodiments tofollow, reference will be made to the attached drawings, in which:

FIG. 1 illustrates longitudinal relaxation time (T1) of blood as afunction of injection imaging time and total paramagnetic contrast dosefor a compound with a relativity of about 4.5/millimolar-second;

FIG. 2 illustrates calculated magnetic resonance signal intensity as afunction of flip angle for 5 different longitudinal relaxation times(T1) assuming a spoiled, 3D volume acquisition with TR equal to 25 msecand TE<<T2*;

FIGS. 3, 4, 5A and 5B, and 6A-C are block diagram representations ofmechanical infusion devices and configurations, according to the presentinvention;

FIG. 7 is a block diagram representation of a manual injectionconfiguration, according to the present invention;

FIGS. 8A-C illustrate typical coronal maximum intensity projection (MIP)collapse images obtained (FIG. 8A) prior to injection of gadopentetate.dimeglumine, (FIG. 8B) dynamically during intravenous injection ofgadopentetate dimeglumine, 0.2 millimoles/kilogram over 5 minutes, and(FIG. 8C) immediately following injection of gadopentetate dimeglumine;

FIG. 9 illustrates region of interest analysis averaged for threepatients who had pre-infusion, dynamic infusion, immediate post infusionand delayed 3D FT imaging. This figure shows that there is a shortwindow, during contrast infusion, when the aorta signal intensity (solidsquares) is higher than that of the IVC (open squares) and backgroundtissues, fat (diamonds) and muscle (triangles);

FIG. 10A is an illustrative example of a magnetic resonance image of apatient with an abdominal aortic aneurysm. The magnetic resonanceangiography (“MRA”) depicts the aneurysmal aorta and aneurysmal commoniliac arteries as well as severe stenoses of the right external iliac(curved arrow) and inferior mesenteric (straight arrow) arteries and amild stenosis of the left common iliac artery;

FIG. 10B illustrates a digital subtraction angiogram of the aneurysmalaorta and aneurysmal common iliac arteries as well as severe stenoses ofthe right external iliac (curved arrow) and inferior mesenteric(straight arrow) arteries and a mild stenosis of the left common iliacartery of FIG. 10A;

FIG. 11 is a block diagram representation of one embodiment of thepresent invention (imaging system, infusion system and detectionsystem);

FIG. 12 is a detailed block diagram representation of one embodiment ofthe detection system in conjunction with the imaging system and theinfusion system;

FIG. 13A is an illustration of the appendage cushions in relation to apatient and in conjunction with a portion of the infusion system; and

FIG. 13B is a cross-sectional view of the appendage cushions of FIG. 13Ataken along line a—a.

DETAILED DESCRIPTION

The present invention is a system and technique for providingpreferential enhancement of arteries relative to adjacent veins andbackground tissue by correlating the collection of a predeterminedportion of data of a magnetic resonance contrast image with the arterialphase of the magnetic resonance contrast enhancement. The arterial phaseof the contrast enhancement may be described as a period of a maximum,elevated, and/or substantially elevated contrast concentration in theartery (arteries) relative to adjacent veins. The arterial phase ofcontrast enhancement may also be described as a period during which theconcentration of contrast agent in the artery of the region of interestis about a factor of two greater than a base line or pre-injectionresponse from the region of interest (i.e., the response of the regionof interest to a series of magnetic resonance pulses prior toadministration of a magnetic resonance contrast agent to the patient).

The system and technique of the present invention synchronizes thecollection of a predetermined portion of image data with the arterialphase of contrast enhancement. The present invention includes adetection system, a magnetic resonance imaging system and an infusionsystem. The detection system monitors and detects the relativeconcentration of magnetic resonance contrast agent in the region ofinterest (artery and tissues in a region of interest). The imagingsystem collects image data which is used in generating a magneticresonance image of the region of interest. The imaging system may be anysuitable magnetic resonance imaging system. Finally, the infusion systemadministers the magnetic resonance contrast agent to the patient in acontrolled manner.

Briefly, by way of overview, the detection system facilitates precisesynchronization between the collection of a predetermined portion ofimage data and a portion of the arterial phase of contrast enhancement.Here, the detection system compares the response of a region of interestbefore the administration of magnetic resonance contrast agent (e.g.,gadolinium) to the patient to the response of the region of interestduring and/or after administration of the contrast agent. When acharacteristic change in the response to the magnetic resonance pulse ismeasured by the detection system, the imaging system collects apredetermined portion of image data (e.g., data representative of thecenter of k-space).

In particular, prior to administration of a magnetic resonance contrastagent, the imaging system applies a series of magnetic resonance pulses(radio frequency pulses) to a region of interest in the patient. Thedetection system measures or determines a base line or pre-contrastresponse of the region of interest (artery and/or tissues in the regionof interest) to that series of pulses. The series of magnetic resonancepulses are applied to the patient to tip the longitudinal magnetizationof protons in the region of interest and measure the response of theregion of interest before administration of the contrast agent to thepatient. The response signal (in the radio frequency range) from theregion of interest is monitored using a variety of coils of the magneticresonance imaging system and measured by the detection system.

After the base line or pre-contrast response is measured, the contrastagent may be administered to the patient. Thereafter, the detectionsystem measures (continuously, periodically or intermittently) theresponse from the region of interest to detect the “arrival” of thecontrast agent in the region of interest. In this regard, the imagingsystem applies a series of magnetic resonance pulses and the detectionsystem evaluates the response from the region of interest. When contrastagent “arrives” in the region of interest (artery or arteries ofinterest), the detection system detects a characteristic change in theresponse from the region of interest to the magnetic resonance pulses;that is, the detection system identifies a characteristic change in theradio frequency signal emitted from the region of interest. Thischaracteristic change in radio frequency signal from the region ofinterest indicates that the contrast agent has “arrived” in theartery/arteries in that region.

In those instances where the injection of the contrast agent is of abolus type (i.e., rapid injection), the characteristic change in theresponse to the magnetic resonance pulses may indicate that the regionof interest is in or is “entering” the arterial phase of the magneticresonance contrast enhancement. Where the contrast agent is injectedover a substantial portion of the imaging sequence, detecting thearrival of the contrast agent may indicate that the region of interestis entering the arterial phase of contrast enhancement or will beentering the arterial phase some time in the future depending on a “timedelay” as described below.

In one preferred embodiment, the detection system, upon sensing theregion of interest is in the arterial phase of contrast enhancement(e.g., contrast concentration in the region of interest is above apredetermined level or the contrast concentration in the artery isgreater than that in the surrounding tissues), may instruct the magneticresonance imaging system to initiate acquisition of the predeterminedportion of the imaging data (e.g., data representative of the center ofk-space). The concentration of the contrast in the region of interestmay be detected in a number of different ways including, for example, achange in the shape of the responsive radio frequency signal, a changein the shape of the signal envelope and/or a change in its amplitude.

In another embodiment, an operator may observe a change in the shape ofthe radio frequency signal envelop and/or a change in its amplitudemeasured by the detection system. In response, the operator may instructthe imaging system to initiate an imaging sequence including collectinga predetermined portion of the image data by the magnetic resonanceimaging system. In this embodiment, the operator monitors the detectionsystem to observe the characteristic change in the response from theregion of interest to the plurality of pulses from the imaging system;and, upon observing such a change, the operator may engage the imagingsystem to begin collecting image data of the predetermined imagingsequence.

In one preferred embodiment, the predetermined portion of image data isdata which is representative of the center of k-space (i.e., the lowspatial frequency MR image data), or a portion thereof.

Under the circumstances where the detection system (or operator)instructs the imaging system to collect image data which isrepresentative of the center of k-space upon detecting the start of thearterial phase of contrast enhancement, the magnetic resonance imagingpulse sequence may be arranged such that the central portion of k-spacedata is collected in the beginning or near the beginning of the sequenceand the periphery of k-space is collected thereafter. This providesproper synchronization between the arterial phase of contrastenhancement and the collection of image data which is representative ofthe center of k-space. Moreover, arranging the sequence such that thecentral portion of k-space data is collected in the beginning or nearthe beginning of the sequence insures that a sufficient amount of datawhich is representative of the center of k-space is collected during thearterial phase of contrast enhancement.

In those instances where the arterial phase is “long”, there may be timeto collect the entire image data set during the arterial phase. However,in those instances where the arterial phase is brief, collection ofimage data which is representative of the center of k-space issynchronized with the period of a maximum, substantially elevated, or anelevated contrast concentration in the artery/arteries of interestrelative to adjacent veins.

Where the magnetic resonance pulse sequence is of conventional,sequential type and the data representative of the center of k-space iscollected in the middle of the scan, the detection system may beemployed to determine a “fine adjust” for the infusion rate of thecontrast agent by the infusion system to the patient so that a period ofmaximum, substantially elevated or elevated concentration of contrastagent in the region of interest is correlated to the collection of imagedata which is representative of the center of k-space (i.e., mapping ofk-space). In this embodiment, the detection system monitors the responseof the region of interest to a series of magnetic resonance detectionpulses. When the detection system determines that the contrast has“entered” the region of interest, the detection system (or operator) mayadjust the rate of injection of the contrast agent in order to providesufficient or maximum overlap between the collection of k-space and thearterial phase of the contrast enhancement. The detection system (oroperator) calculates an adjustment to the rate of infusion based onseveral factors including the time between the start of the infusion andthe detection of a change in the response by the region of interest tothe magnetic resonance detection pulses (“circulation time delay”), thetiming of the mapping of k-space, and the current and future rates ofinfusion. The detection system (or operator) may accordingly increase ordecrease the rate of injection to compensate for the “time delay” inorder to provide sufficient or maximum overlap between the mapping ofk-space and the arterial phase of contrast enhancement.

In one embodiment, the monitoring and detecting functions of thedetection system and imaging system of the present invention may bedeferred until the contrast agent is expected in the region of interest.In this regard, the application of the detection pulses (by the imagingsystem) employed to detect/monitor the “arrival” of the contrast agentto the region of interest, may be delayed according to the time delayexpected between the infusion of the contrast to when the contrast“enters” the artery of interest. This will confine the use of thedetection system and the magnetic resonance imaging system to thoseinstances when the contrast agent is expected in the region of interestor when a maximum, elevated or substantially elevated contrast agentconcentration is anticipated. This may be useful when patients need tohold their breath for the entire period of detection and monitoring.

The present invention is well suited for collecting image data forimaging an artery, including the aorta. In this regard, as described andillustrated at length in the related applications indicated above (whichapplications are expressly incorporated herein by reference),correlating a maximum, elevated and/or substantially elevated contrastconcentration in the artery of interest with the collection of imagedata representative of the center of k-space enhances the image of thatartery. The present invention allows for accurately detecting a maximum,elevated or substantially elevated contrast concentration in the arteryof interest relative to surrounding tissues. This facilitates propercorrelation between the collection of image data representative of thecenter of k-space and the arterial phase of contrast enhancement in theartery of interest.

Further, as noted in the related applications, the time between contrastinjection and a maximum, elevated or substantially elevated contrastconcentration in the artery of interest may vary according to a numberof factors including the location of the artery of interest, the size ofthe artery of interest, the physical condition of the patient, and thetime delay due to the configuration of the contrast agent deliverysystem. These factors may not be precisely quantifiable for each andevery patient; and, as a result, it may be difficult to predict (withsufficient precision) for each patient when the period of arterial phaseof contrast enhancement occurs in relation to the mapping of k-space.Thus, it may be difficult to precisely time the contrast injection andthe imaging sequence to properly capture a sufficient amount of thepredetermined image data (e.g., data representative of k-space) duringthe arterial phase of the enhancement of the region of interest. Indeed,in some instances, there may be a tendency to use more contrast agentthan is necessary in order to allow for a longer bolus injection whichwould ensure that the arterial phase is of sufficient duration tooverlap with the collection of image data representative of the centralk-space.

Typically, the delay from the time of administering the contrast agentat a maximum, elevated, or substantially elevated rate to therealization of the arterial phase of contrast enhancement in the regionof interest may be about 10-50 seconds. Such a large range of timedelays may make it difficult to provide sufficient overlap of thearterial phase of contrast enhancement of the region of interest and thecollection of image data representing the center of k-space. The presentinvention, however, “automatically” correlates a period of maximum,elevated or substantially elevated arterial contrast concentration withthe mapping of the center of k-space; that is, the detection systemsynchronizes the collection of image data representative of the centerof k-space with a period of maximum, elevated or substantially elevatedarterial contrast in the artery of interest. This eliminates the need touse “extra” contrast agent to compensate for possible timing errors.

In short, the present invention alleviates any difficulties incollecting image data corresponding to the center of k-space during thearterial phase of contrast enhancement of the region of interest.Moreover, the present invention insures that the arterial phase ofcontrast enhancement extends for a sufficient period of the collectionof image data representing the center of k-space without “wasting” anycontrast agent.

The present invention may be employed in a method and apparatus whichprovides anatomic information, in the form of images, using acombination of a plurality of magnetic resonance angiography sequences,including one spin-echo and four magnetic resonance agent (e.g.,gadolinium) enhanced magnetic resonance angiography sequences. Theanatomic images may be used in, for example, pre-operative, operativeand post-operative evaluation of abdominal aortic aneurysms and/orabdominal aortic aneurysm surgery. The contrast-enhanced magneticresonance angiography provides sufficient anatomic detail to detectaneurysms and all relevant major branch vessel abnormalities seen atangiography or at operation.

An evaluation of abdominal aortic aneurysms and other vascular pathologymay require one, some or all of the following magnetic resonance imagesequences:

(1) an initial T1 weighted sequence; the T1 sequence may be used toidentify the location of the aneurysm. This sequence may also beemployed to define the location of renal and splanchnic arteries forplanning higher resolution gadolinium-enhanced sequences (discussedbelow). Further, the T1 sequence may provide information as to theapproximate size of each kidney, the size of the aneurysm, and thelocation of the left renal vein. A preferred orientation of thissequence is in the sagittal plane;

(2) a dynamic gadolinium-enhanced 3D volume sequence; the 3D volumesequence may be obtained in the coronal plane and reconstructed intosagittal, axial and/or oblique projections to produce images that aresimilar to biplane aortography or helical CT angiography. In a preferredembodiment, these images are employed to evaluate the renal andsplanchnic artery origins, the iliac arteries, and the distal extent ofthe aneurysm;

(3 and 4) sagittal and axial 2D time-of-flight images; the sagittal andaxial 2D time-of-flight images demonstrate the maximum size of theaneurysm, its proximal extent and peri-aneurysm inflammation. Thesagittal and axial 2D time-of-flight images may be employed to detectthe presence of thrombus and the features of the thrombus, including itslocation, surface irregularity and/or enhancement; and

(5) 3D phase contrast images; the 3D phase contrast volume imagesdefines the renal arteries in greater detail to facilitate grading theseverity of occlusive lesions.

In addition, in one embodiment, the present invention may be implementedin a technique and apparatus wherein a combination ofgadolinium-enhanced magnetic resonance angiographic sequences are usedto provide a highly accurate mechanism for detecting, examining andgrading occlusive lesions. Such information is valuable during manystages of evaluation of the patients.

EXAMPLE 5, set forth in detail below, defines the imaging parameters ofthe magnetic resonance image sequences (initial sagittal T1 sequence,dynamic gadolinium-enhanced 3D volume sequence, sagittal and axial 2Dtime-of-flight images, and 3D phase contrast images).

The sequence of imaging the abdominal aorta, as outlined above, may beemployed in different combinations for providing anatomic images of theaorta. Under some circumstances when imaging abdominal aortic aneurysms,not all of sequences are necessary. An imaging technique using one orseveral of the sequences may provide limited information of, forexample, the distal end of the aneurysm (dynamic gadolinium enhanced 3Dvolume imaging sequence) and the maximum size of the aneurysm (sagittaland axial 2D time-of-flight images). One skilled in the art wouldrecognize that other permutations of the sequences are possible and thenumber and combination of the sequences may be tailored according to theinformation needed or desired.

Further, several of the sequences may be repeated or omitted accordingto the information desired. In those instances where sequences arerepeated, the information collected may be employed to check or verifythe imaging results which are obtained from other sequences. Thus, inshort, numerous permutations of sequences may be implemented to providevarying degrees of evaluation, as well as certainty, of abdominal aorticaneurysms. A combination of these sequences may be used to evaluatepatients suspected of having other pathology, such as renal arterystenosis or mesenteric ischemia.

The magnetic resonance angiography sequences for generating the imagedata may be performed during or following infusion of magnetic resonancecontrast agent (e.g., gadolinium). Under this circumstance, the systemand technique of the present invention may be employed to properlycorrelate the maximum, elevated or substantially elevated concentrationof contrast in the region of interest with the collection of image datarepresentative of the center of k-space. Employing the technique andsystem of the present invention, the mapping of k-space of one or moreof the magnetic resonance angiography sequences may be preciselycorrelated with the time at which the region of interest possess amaximum, elevated or substantially elevated contrast concentration.Thus, it may be unnecessary to “manually” calculate the propercorrelation of a maximum, elevated or substantially elevated rate ofinfusion and the mapping of k-space according to the location of theartery of interest, the size of the artery of interest, the physicalcondition of the patient, the time delay due to the configuration of thecontrast agent delivery system, and/or the type of pulse sequenceemployed by the imaging apparatus

In a preferred embodiment, the magnetic resonance contrast agent isadministered in a vein which is remote from the artery in the region ofinterest (i.e., the artery under study). The magnetic resonance contrastagent may be injected using a number of different parameters, systemsand/or techniques.

In one embodiment, the magnetic resonance contrast agent may be injectedinto a patient (a human or other animal) for example, substantiallythroughout the period of imaging in a controlled manner (i.e., injectedat a controlled rate over the period of imaging). A substantial portionof the data collection time is a majority of the time and should includethe period of time during which the center of k-space is acquired. Underthis circumstance, as mentioned above, the detection system may beemployed to adjust the rate of infusion of the infusion device toprecisely correlate a period of maximum, elevated or substantiallyelevated arterial contrast concentration in the region of interest withthe mapping the center of k-space. In this embodiment, the detectionsystem detects the arrival of the contrast agent in the region ofinterest and, in response, adjusts the rate of injection of the contrastso that when the imaging system collects image data which isrepresentative of the center of k-space, the region of interest has amaximum, elevated or substantially elevated concentration of contrast.That is, the detection system “fine tunes” the rate of injection ofcontrast so that the desired arterial contrast concentration occurswhile mapping the center of k-space. Thus, the detection system of thepresent invention insures that the region of interest is in the arterialphase of contrast enhancement during at least a portion of thecollection of image data representing the center of k-space.

In another embodiment, the injection is a bolus type (i.e., rapidly).Under this circumstance, in a preferred embodiment, the detection systemdetects a characteristic change in the response by the region ofinterest and, in response thereto, instructs the imaging system tocollect image data which is representative of the center of k-space. Theimaging system collects the image data corresponding to the center ofk-space in the beginning or near the beginning of the scan.

The present invention may utilize a number of different magneticresonance contrast agents. In this regard, the magnetic resonancecontrast agents are well known in the art, and are disclosed in, forexample, U.S. Pat. Nos. 5,141,740; 5,078,986; 5,055,288; 5,010,191;4,826,673; 4,822,594; and 4,770,183, which are incorporated herein byreference. Such magnetic resonance contrast agents include manydifferent paramagnetic contrast agents, for example, gadoliniumcompounds. Gadopentetate dimeglumine, gadodiamide and gadoteridol areparamagnetic gadolinium chelates that are readily available, and whichrapidly redistribute into the extracellular fluid compartment. Othergadolinium compounds are acceptable, and may have a higher relaxivity,more rapid redistribution into the extracellular fluid compartment, andgreater and faster extraction in the capillary bed. It should be notedthat contrast agents that are extracted or degrade in or near thecapillary bed are preferred for the present invention.

In one preferred embodiment, when performing at least one of themagnetic resonance angiography sequences, the injected contrast agentshould be sufficiently small to rapidly redistribute into theextracellular fluid compartment in the systemic capillary bed, or thecontrast agent should be actively extracted from the circulation in thecapillary bed distal to the artery of interest, or both. Under thesecircumstances, the artery (or arteries) of interest contains a highconcentration of contrast and the vein (or veins) adjacent to the artery(or arteries) of interest possesses a lower contrast concentration.Further, under these circumstances, the relationship of artery-to-venouscontrast concentration is substantially maintained over the period ofcontrast injection.

Matching the duration of the injection with the time required for alongitudinal relaxation time (T1) weighted magnetic resonance image dataset, may provide the situation where it is possible to view the arteriesdistinct from the veins. Further, by injecting the contrast at asufficient rate, the longitudinal relaxation time of the arterial bloodmay be made sufficiently short when compared to that of the backgroundtissues. As a result, the image of the arteries is distinct frombackground tissue as well.

As mentioned above, an advantage of the present embodiment is theprecise accuracy in synchronizing the collection of the center ofk-space with a maximum or elevated concentration of the contrast agentin the artery of interest—for each and every scan or sequence.Compensating for the timing of the infusion of the magnetic resonancecontrast agent may be unnecessary since the detection system identifieswhen the artery of interest includes a maximum, elevated orsubstantially elevated arterial contrast concentration. Thus, employingthe detection technique of the present invention alleviates the need to“manually calculate” the correlation of the maximum or elevated rate ofinfusion with the mapping of k-space accounts for the time delay due tothe contrast agent delivery system (e.g., the length of catheter whichdelivers the contrast agent) and/or the time-delay due to the timerequired for the contrast agent to circulate from the site of injection,through the body, and into the artery of interest.

It should be noted that the center of k-space may be characterized as10% to 75% of the total k-space data which, as indicated above,corresponds to the lowest spatial frequency information.

It should be further noted that when imaging larger arteries during themagnetic resonance angiography sequence, in a preferred embodiment, anelevated, substantially elevated or maximum concentration of contrastagent in the artery of interest is typically provided for at least 20%of the time during which image data corresponding to the center ofk-space is collected; and preferably, an elevated, substantiallyelevated or maximum concentration of contrast in the artery of interestis maintained for between 20% to 50% of the mapping of the center ofk-space. This, translates into correlating a period of substantiallyelevated or maximum rate of injection with the period of collection ofimage data corresponding to the center of k-space so that during atleast 20% of the time of mapping k-space, a substantially elevated ormaximum concentration of contrast agent is maintained in the artery ofinterest relative to adjacent veins; and preferably about 50%.

When imaging smaller arteries, in a preferred embodiment, an elevated ormaximum concentration of contrast agent in the artery of interest isprovided for greater than 50% of the time during which image datacorresponding to the center of k-space is collected; and in a morepreferred embodiment, an elevated or maximum concentration of contrastin the artery of interest is maintained for greater than 75% of themapping of the center of k-space. As a result, where the artery ofinterest is relatively small, the administration of the contrast agentmay include a maximum or elevated rate of injection of the contrastagent of greater than 50% of the time of mapping of the center ofk-space; and preferably between 50% to 85%, and most preferably greaterthan 75%. Under this circumstance, fewer artifacts are observed in thesmaller vessels or arteries when the contrast is administered at amaximum or elevated rate over a longer period of the k-space mapping.

Further, during the acquisition of magnetic resonance angiographic imagedata corresponding to the center of k-space, it may be important toavoid excessively rapid changes in arterial contrast concentration.Rapidly changing blood signal during acquisition of the center ofk-space may create image reconstruction artifacts. These artifacts maybe minimized when the arterial signal intensity is uniform. Further,these artifacts may be minimized by avoiding rapid changes in thearterial contrast concentration during acquisition of image data andespecially during acquisition of the center of k-space.

In those instances where the invention is implemented using paramagneticcontrast agents, in a preferred embodiment, infusion is at a rate thatwill provide a concentration of the agent in the arteries, such that thearteries will have at least 50% more signal than any backgroundstructures, including veins, in the final image. In another preferredembodiment, the concentration of contrast agent will cause thelongitudinal relaxation time (T1) of the protons in the arteries to beshorter than protons in any of the background material. Where thecontrast agent causes the arteries to appear black in the final image(e.g., where the contrast agent shortens T2*, for example, some Fepowders), the contrast agent should be infused at a rate and amount toinsure that the effective transverse relaxation time (T2*) in thearteries is shorter than in any of the background material.

Magnetic Resonance Imaging System

Any magnetic resonance imaging (MRI) system suitable for imaging aportion of an animal body, for example, a human, may be used foracquisition of image data in the method of this invention. Inparticular, apparatus and imaging methods for magnetic resonanceangiography are known in the art (see, e.g., U.S. Pat. Nos. 4,718,424;5,034,694; and 5,167,232, incorporated herein by reference), and thesemay be used with the method of MRA with dynamic intravenous injection ofmagnetic resonance contrast agents taught herein, subject only to theconstraints taught below.

The parameters of the imaging method of the magnetic resonanceangiography sequences are discussed immediately below with respect togadolinium chelates. The Examples described thereafter includeadditional imaging parameters. It should be noted, however, that othermagnetic resonance contrast agents may be employed in practicing thepresent invention including paramagnetic contrast agents, such as thosedescribed by Marchal, et al., in Potchen, et al., eds., supra, pp.305-322, the text of which is incorporated herein by reference.

Injection Parameters

Gadolinium chelates are paramagnetic agents which shorten thelongitudinal relaxation time, T1, of blood according to EQUATION 1:$\begin{matrix}{\frac{1}{T1} = {\frac{1}{1200} + {{Relaxivity} \times \lbrack{Gd}\rbrack}}} & (1)\end{matrix}$

where: (1) the longitudinal relaxation time (T1) of blood withoutgadolinium is 1200 milliseconds; and

(2) [Gd] is the blood concentration of a gadolinium chelate.

With reference to EQUATION 1, to achieve an arterial blood (T1) that isshort compared to adjacent fat (T1=270), it is necessary tosubstantially elevate the arterial blood concentration of the contrastagent in the artery of interest to be greater than ({fraction (1/270)}milliseconds-{fraction (1/1200)} milliseconds)/relaxivity of thecontrast agent (or 2.9/seconds*relaxivity). Thus, the artery of interestincludes a substantially elevated concentration of the contrast agentwhen that concentration is greater than 2.9 seconds⁻¹ relaxivity⁻¹ ofthe contrast agent.

A substantially elevated rate of infusion provides a substantiallyelevated concentration of the contrast agent in the artery of interest.That is, a substantially elevated rate of infusion provides an arterialblood concentration of the contrast in the artery of interest which isgreater than 2.9 seconds⁻¹ relaxivity⁻¹ of the contrast.

As reflected in EQUATION 2, below, the arterial blood [Gd] may beexpressed in terms of the intravenous injection rate and the cardiacoutput during dynamic imaging at times short as compared to therecirculation time. $\begin{matrix}{\lbrack{Gd}\rbrack_{arterial} = {\frac{{Injection}\quad {Rate}}{{Cardiac}\quad {Output}} + \lbrack{Gd}\rbrack_{venous}}} & (2)\end{matrix}$

As long as the gadolinium chelate is sufficiently small, the gadoliniumchelate will rapidly redistribute into the extracellular compartment asit passes through the capillary bed and the venous concentration will below or negligible compared to the arterial concentration. Therelationship between the longitudinal relaxation time of arterial bloodand the injection rate may then be determined by combining EQUATION 1and EQUATION 2, as stated below in EQUATION 3: $\begin{matrix}{{{Injection}\quad {Rate}} = {\frac{\left\lbrack {\frac{1}{T1} - \frac{1}{1200}} \right\rbrack}{Relaxivity} \times {Cardiac}\quad {Output}}} & (3)\end{matrix}$

To achieve contrast between arterial blood and background tissue, thelongitudinal relaxation time of the arterial blood should be reduced toless than that of the background tissues. Of all types of backgroundtissues, fat (T1=270 msec) typically has the shortest longitudinalrelaxation time. Assuming a typical minimum resting cardiac output of0.0005 Liters/Kg-sec and requiring the longitudinal relaxation time tobe less than 270 milliseconds simplifies EQUATION 3 to EQUATION 4 asshown below: $\begin{matrix}{{{Injection}\quad {Rate}} > \frac{0.0015\quad {L/{Kg}}{\text{-}\sec^{2}}}{Relaxivity}} & (4)\end{matrix}$

By way of example, gadopentetate dimeglumine, gadodiamide, andgadoteridol are three paramagnetic gadolinium chelates that are readilyavailable and rapidly redistribute into the extracellular fluidcompartment. The relaxivities of gadopentetate dimeglumine andgadoteridol are about 0.0045/molar-second. Based upon the aforementionedand using EQUATION 4, the minimum injection rate is greater than 0.033millimole/Kg-minute.

With continued reference to EQUATION 4, a rate of infusion which isgreater than 0.0015 Liters/Kg-sec² divided by the relaxivity may providea maximum concentration of the contrast agent in the artery of interest.That is, infusing the contrast into the patient at a rate of greaterthan 0.0015 Liters/Kg-sec² divided by the relaxivity may yield a maximumarterial blood concentration of the paramagnetic contrast agent.

The total dose of gadolinium chelate required may be determined bymultiplying the injection rate by the imaging time. For a relaxivity of4.5/millimolar-second, and an imaging time of 5 minutes (300 seconds),the dose should substantially exceed 0.1 millimole/kilogram.

The dose of the gadolinium chelate may be within the range of 0.05millimoles/kilogram body weight to 1 millimoles/kilogram body weightdepending upon the time required to obtain the image. It should be notedthat the dose of the contrast should not be too high such that there maybe undesirable toxicity or T2 effects. In a preferred embodiment, thedose of the gadolinium chelate is within the range of 0.2millimoles/kilogram body weight to 1 millimoles/kilogram body weight. Ina more preferred embodiment, the dose of the gadolinium chelate is about0.3 millimoles/kilogram body weight.

When injecting by hand or with simple pumps, it may be convenient togive all of the patients the same volume of contrast agent. In this waythe operator may get accustomed to timing the injection of a standardinfusion volume to provide proper correlation between an elevatedconcentration of contrast agent in the region of interest to thecollection of image data representative of the center of k-space. Inthose instances where the contrast agent is a gadolinium contrast, apreferred standard volume is 40 to 60 ml.

In those instances where the contrast injection times are longer thanthe recirculation time, the longitudinal relaxation time of arterialblood tends to be even shorter since a fraction of the gadoliniumchelate will recirculate. It should be noted that a T1 of 270 ms(corresponding to the brightest background tissue fat) is equivalent toa gadopentetate dimeglumine concentration of about 0.6 millimole/liter.

FIG. 1 illustrates the longitudinal relaxation time (T1) of blood as afunction of infusion time and the total paramagnetic contrast dose for aparamagnetic contrast compound having a relaxivity of4.5/millimolar-second. An examination of FIG. 1 reveals that theshortest T1 occurs with the shortest infusion time and the largestgadolinium dose. For typical imaging times of 3 to 5 minutes, FIG. 1further reveals that the dose should be of the order of 0.2millimoles/kilogram or larger in order to achieve a longitudinalrelaxation time of blood significantly shorter than that of thebrightest background tissue fat (T1=270) for the entire duration ofimaging.

It should be noted that higher doses of gadolinium and gadoliniumchelates with higher relaxivity may also improve image quality.

Imaging Parameters

Any suitable T1 weighted magnetic resonance imaging sequence may be usedduring injection of the paramagnetic contrast. Suitable imagingsequences will be readily apparent to the skilled practitioner and aredescribed in Potchen, et al., eds., supra. The following criteria forselection of preferred imaging parameters are based on experience inover 100 patients on a 1.5 Tesla General Electric signa magnet withversion 4.7 or higher software. A three-dimensional Fourier Transform(volume) acquisition (3D FT) is preferred in the abdomen because of itsintrinsically high spatial resolution and high signal-to-noise ratio,even with a large, body coil. The gradient echo (gradient recalled)pulse sequences are preferred since they allow a short TR (repetitiontime) which allows a shorter imaging acquisition time. Short imagingtimes have the advantage of allowing the same total gadolinium dose tobe injected at a faster rate.

Spoiled Versus Non-Spoiled Gradient Echo Imaging

It should be noted that one might expect steady state gradient echoimaging (GRASS) to be preferable to the spoiled gradient echo imagingbecause the long T2 (transverse relaxation time) of blood increases thesteady state blood signal. However, this effect enhances veins more thanarteries, because the fast, pulsatile flow of arterial blood spoils itssteady state component. In theory, this may have the paradoxical effectof reduced arterial contrast. In practice, there may only be a smalldifference between the spoiled and unspoiled techniques. In patientswith slow arterial flow (which is not self-spoiling), a steady stategradient echo pulse sequence may be preferred. A spoiled gradient echopulse sequence (SPGR) was chosen for most of the studies describedherein to simplify the theory and analysis as well as to reduce thepotential for differential steady state magnetization between arterialblood, slower venous blood and background tissue.

Echo Time

Because the brightest background tissue is fat, it is preferable to usea TE (echo time) where fat and water are out of phase, thereby achievingan incremental improvement in vessel-to-background contrast. At 1.5Tesla, this occurs about every 4.6 msec beginning at about 2.3 msecwhich corresponds to a TE of 2.3, 6.9, 11.5, . . . msec. The shortest ofthese possible TE values (6.9 or about 2.3 msec in the studies describedherein) is preferred. Shorter TE's tend to minimize the effects ofmotion related phase dispersion.

Repetition Time

In a preferred embodiment, TR should be as short as is possible. A TR of24-25 msec was the shortest possible on the equipment used for thestudies described in EXAMPLES 1-3. As the TR is shortened, the flipangle must be adjusted to maintain the optimal T1 weighing.

Flip Angle

With a gadolinium chelate dose of 0.2 millimoles/kilogram and a 3-5minute injection time and imaging time, the longitudinal relaxation timeof the arterial blood is predicted to be in the order of 150 to 200milliseconds. It will, however, be shorter as a result of therecirculation time being less than 3-5 minutes. The relative signalintensity, SI, in a 3D FT spoiled gradient echo acquisition as afunction of blood T1, TR, T2, T2*, flip angle σ, and proton density N(H)may be expressed as stated in EQUATION 5, below, and calculatedaccordingly. $\begin{matrix}{{SI} = {{N(H)}\frac{1 - {\exp \left( {- \frac{TR}{T1}} \right)}}{1 - {\cos \quad (\alpha)\quad \exp \quad \left( {- \frac{TR}{T1}} \right)}}\sin \quad (\alpha)\quad \exp \quad \left( {- \frac{TE}{{T2}^{*}}} \right)}} & (5)\end{matrix}$

FIG. 2 graphically illustrates relative signal intensity for T1 equal to50, 100, 150, 270 (fat), and 1200 (blood) under the followingconditions: (1) TR=25 milliseconds, and assuming TE is small compared toT2* (the observed transverse relaxation time) FIG. 2 reveals that a flipangle of about 40 degrees is optimal for maximizing blood-to-backgroundtissue (fat) contrast when the longitudinal relaxation time (T1) ofblood is of the order of 200 milliseconds. For larger gadolinium doseswith faster injection rates, a larger flip angle may be moreappropriate.

Volume Orientation

In order to minimize the image acquisition time, the imaging volumeshould be made as thin as possible while containing the arteries ofinterest. In this regard, it may be useful to orient the image volumefor maximum in-plane coverage of the vessels of interest as opposed tothe perpendicular orientation required for optimal time-of-flightmagnetic resonance angiography. Optimizing the orientation andminimizing the thickness of the imaging volume is facilitated by firstacquiring a conventional black-blood or time-of-flight MRI to use as aguide for precise localization. Phase and frequency encoding axes shouldbe oriented such that cardiac and respiratory motion artifacts do notsuperimpose on the vessels of interest. Generally, for imaging theaorta-iliac system, the imaging volume should be oriented coronally, andthe phase encoding axis should be set right-to-left. For imaging thethoracic aorta, a sagittal orientation is preferred and for imaging thesubclavian arteries, an axial orientation is preferred.

Partitions

The number of partitions (slices) is determined by the thickness of theimage volume divided by the partition thickness. The partition thicknessis the image resolution along the axis perpendicular to the plane of thepartitions. It may be useful to employ thin partitions in order to havehigh image resolution. The image acquisition time, however, linearlyincreases with the number of partitions. As a result, keeping the imageacquisition time short requires minimizing the number of partitions.

It should be noted that there may be a loss of signal-to-noise as thevoxel size is decreased by using higher resolution pixels. Generally,0.5 to 3 millimeter resolution with 28 to 60 partitions is adequate forthe aorta and major branch vessels. The skilled practitioner willbalance the need to increase resolution by decreasing voxel size withthe need to avoid excessive periods of time to acquire image data.

Field-of-View

The field-of-view must be made large enough to avoid excessivewrap-around artifact. Wrap around artifacts occur when there arestructures outside the field of view along the phase encoding axis.These structures are mapped by the phase encoding process to superimposeon structures within the field of view.

In addition, because of the limited number of pixels along the frequencyencoding axis and the time penalty for each additional pixel along thephase encoding axis, it is also desirable to make the field-of-view assmall as possible in order to maximize image resolution with the minimumimage acquisition time. Generally, for imaging the abdominal or thoracicaorta, a field-of-view of about 36 centimeters is appropriate for mostpatients. It may be increased for larger patients and reduced forsmaller patients. Smaller field-of-views may be used for other parts ofthe body.

Use of a no-phase wrap algorithm is a less preferred embodiment. Underthe circumstance of this invention, this has a disadvantage of generallyrequiring more imaging time and, as a result, a larger gadolinium dose.

Coils

It is preferable to use the smallest possible coil in order to minimizenoise. There is also an advantage to coils that encircle the body partof interest such that the signal will be homogeneous throughout theentire field-of-view. It may be useful to use a coil with quadature.

Patient Positioning

The patient should be positioned such that the body part being imagedremains stationary during the acquisition of image data.

Cardiac and Respiratory Motion Compensation

The phase artifact related to respiratory and cardiac motion may beminimized by combining the T1 weighted imaging sequence with respiratoryor electrocardiographic gating. Gating has the disadvantage ofincreasing the scan time—particularly in patients with irregularrhythms. Compensation techniques in which the acquisition of the imagedata in k-space is matched to the respiratory and or cardiac cycle mayeliminate some phase artifact without significantly increasing the scantime.

In imaging regions of the body that move substantially with respiration(e.g., the renal arteries) it may be useful to acquire data while thepatient is holding his breath. This may require shortening the durationof the image acquisition time to under one minute. If the patient cannothold his breath for the entire period of image acquisition, than it maybe useful to hold the breath during acquisition of image datacorresponding to the center of k-space and breathing only duringacquisition of data corresponding to the periphery of k-space. Examples6 and 7 discuss the parameters and results of a breath hold imagingtechnique.

To facilitate breath holding during acquisition of image data which isrepresentative of the central portion of k-space (i.e., the central halfof k-space) it may be advantageous to order or arrange k-spacecentrically or in a shifted fashion so that the center of k-space isacquired in the beginning of the scan. In this way, if the patientbegins breath holding at the beginning of the scan, the breath holdingwill automatically coincide with the collection of image data which isrepresentative of the center of k-space. It may, however, be necessaryto have a series of radio frequency pulses precede the center of k-spaceso that the background tissues reach their equilibrium degree ofsaturation. A few seconds of radio frequency pulses are sufficient inmost cases for the tissues to reach dynamic equilibrium.

Pre-scanning

The pre-scanning process is used to tune to the optimum frequency and tooptimize the receiver gain. In the pre-scanning process, it is necessaryto compensate for the changes in the patient's magnetic resonance signalthat will occur during the contrast injection. In those instances whenthe paramagnetic contrast agent is a gadolinium chelate, it ispreferable to tune to the water peak. About a 20% to 50% margin shouldbe incorporated into the receiver gain setting to allow for increasedsignal during contrast administration corresponding to contrast arrivingin the volume of interest.

Premedication

Premedicating patients with an analgesic or sedative such as diazepammay be useful for at least two reasons. Firstly, it may help the patientto tolerate the claustrophobic sensation of being within the magnetthereby reducing voluntary motion artifacts. Secondly, and moreimportantly, its relaxation and cardiac depressant effects tend toreduce the cardiac output. A lower cardiac output results in a higherarterial contrast concentration which thereby improves the imagequality. This result is opposite from conventional magnetic resonanceangiography which is degraded when the cardiac output decreases. Byreducing the cardiac and respiratory rates, analgesics and sedatives mayminimize the fraction of the image acquisition that is adverselyaffected by cardiac and respiratory motion artifacts.

Magnetic Resonance Contrast Agents

As mentioned above, many different magnetic resonance contrast agentsmay be employed when implementing the present invention; for example,numerous paramagnetic contrast agents are suitable. As mentioned above,gadolinium compounds, for example, paramagnetic gadolinium chelates,such as gadopentetate dimeglumine, gadodiamide, and gadoteridol, arereadily available and rapidly redistribute into the extracellular fluidcompartment. Other gadolinium compounds are acceptable. In general,preferred contrast agents have a high relaxivity, rapid redistributioninto the extracellular fluid compartment, and are readily extracted fromthe capillary bed. It should be noted that, contrast agents that areextracted or degrade in the capillary bed are preferred in the presentinvention.

In particular, gadolinium chelates are commercially available from suchcompanies as Bracco (under the name “ProHance”), Berlex (under the name“Magnevist”), and Nycomed USA (under the name “OmniScan”). It should benoted that the gadolinium chelate which is commercially available fromNycomed appears to facilitate greater contrast enhancement between theartery and the surrounding veins and tissue.

Overview of Hardware

With reference to FIG. 11, the present invention includes an infusionsystem 10, a magnetic resonance imaging system 16 and detection 110.Briefly, the infusion system 10 includes infusion device 12 andassociated hardware which facilitates in the administration of themagnetic resonance contrast agent to the patient. The infusion device 12may include a syringe or may be a mechanical type device under thecontrol of the detection system 110 and/or an operator. The infusionsystem 10 is discussed in more detail below.

The magnetic resonance imaging system 16 collects image data which maybe used to generate an image of the region of interest. The imagingsystem 16 may be a commercial magnetic resonance imaging system(including both hardware and software), for example a General ElectricSigna Magnet using version 4.7, 5.2, 5.3, 5.4 or 5.5 software) which issuitable for imaging a portion of an animal body, for example, a human.In addition, the software used with the commercial magnetic resonanceimaging system may be modified to accommodate several of the embodimentsdescribed herein, including collecting image data which isrepresentative of the center of k-space in the beginning of the imagingsequence.

The detection system 110 monitors and detects the arrival of themagnetic resonance contrast agent in the artery and/or tissues in aregion of interest. The detection system 110, in a preferred embodiment,monitors the region of interest to correlate collection of image datarepresentative of the center of k-space with a maximum, elevated orsubstantially elevated concentration in the artery of interest. Thedetection system 110 is discussed in detail below.

Injection

In a preferred embodiment, the type or form of injection of theparamagnetic contrast is intravenous. The injection of the paramagneticcontrast is performed intravenously in order to eliminate or reduce thecomplications associated with the catheterization required for arterialinjections.

The specific site of injection is important for several reasons. Thesite of injection should be remote from the “region of interest”; thatis, the region that is to be scanned. For example, when imaging theabdominal aorta, intravenous injection of the paramagnetic contrast intoan arm vein is preferred (See, FIG. 13B). Use of a leg vein should beavoided. Further, there may be some benefit in avoiding the antecubitalfossa because the patient may bend the elbow during a long (3-5 minute)period of injection which may result in extravasation of the contrastinto the subcutaneous tissues. As a result, under this condition, aforearm or upper arm vein may be preferable.

It should be noted, however, that when the injection is by rapidinfusion (i.e., less than one minute in duration) the antecubital veinmay be preferred because of its close proximity to the heart compared tothe forearm and hand.

In those instances where an artery in the arm is to be imaged, the siteof the injection may be a leg vein or a vein in the opposite arm. Here,the site of injection is remote from the “region of interest”, i.e., theartery in the arm.

Moreover, it is important to correlate a maximum, elevated orsubstantially elevated concentration of contrast agent in the artery ofinterest relative to adjacent veins with the mapping of k-space. Thisensures that the image data representative of the center of k-space iscollected over some period during which a maximum, elevated orsubstantially elevated concentration of contrast agent is maintained inthe artery of interest relative to adjacent veins. The detection system(discussed in detail below) monitors the artery of interest so that thecollection of image data representative of the center of k-spacecoincides with an elevated arterial contrast concentration.

In a preferred embodiment, as illustrated in FIGS. 3 and 4, infusionsystem 10 includes a mechanical infusion or injection device 12. Theinfusion device 12 is an automated type of injector having reliable,consistent and controllable operating conditions. The infusion device 12is employed to inject the magnetic resonance contrast agent into thevein of the patient at an infusion rate sufficient to provide contrastenhancement of an image of an artery relative to veins in the field ofview of the magnetic resonance image and substantially throughout theperiod of acquisition of image data. The infusion device 12 couples tothe patient using conventional techniques, for example, appropriatelyselected tubing 14 which permits fluid flow between the mechanicalinfusion device 12 and the patient. Such tubing may be, for example, anangiocatheter.

A mechanical injector is preferred over manual/operator injectionbecause of the greater reliability, consistency, and controllabilitywhen compared to injecting by hand. Moreover, a mechanical injectorfacilitates the implementation of a fully automated infusion, imagingand detection system of the present invention. In this regard, thedetection system of the present invention may control several of theinfusion parameters of the infusion system.

Since the magnetic field interferes with normal functioning ofelectronic devices, a pneumatic powered, spring loaded or othernon-electric pump may be suitable. It should be noted, however, that anelectrical pump may be used if its operation is unaffected by theoperation of the magnetic resonance imaging system, e.g., if the pump isadequately shielded or if it is located sufficiently far from themagnet.

In one preferred embodiment, the mechanical infusion device 12 iscoupled to the magnetic resonance imaging system 16 to facilitate properor desired timing between the injection of the magnetic resonancecontrast agent and the acquisition of the image data, in addition toproviding proper or desired rates of infusion of the contrast agent.

In another preferred embodiment, proper or desired timing and rates ofinfusion of the contrast agent are controlled through a controlmechanism in the mechanical infusion device 12. That is, the mechanismthat controls the infusion timing and rates of infusion is implementedwithin the mechanical infusion device 12. In this circumstance, themechanical infusion device 12 is a “self-contained” unit. For example,the infusion rate may be controlled with an adjustable fluid flowresistor.

As mentioned above, the infusion device 12 injects the magneticresonance contrast in a controlled manner. The contrast may be containedin a vessel. As illustrated in FIGS. 3 and 4, the mechanical infusiondevice 12 is coupled to a vessel 18 which contains the magneticresonance contrast agent. In one embodiment, the vessel 18 may contain asufficient quantity of contrast agent for one application of theinvention or one sequence of the plurality of the magnetic resonanceangiography sequences, e.g., a single use vessel. In an alternativeembodiment, the vessel 18 may contain a quantity which allows severalapplications of the invention, e.g., a reservoir type of vessel. As isillustrated in FIG. 3, the mechanical infusion device 12 may be adaptedto receive the vessel 18 somewhat like a fountain pen receiving an inkcartridge. In an alternative embodiment, as illustrated in FIG. 4, theinfusion device 12 may be coupled to the vessel 18 using conventionalmethods.

FIGS. 5A and 5B illustrate a mechanical infusion device 12 in moredetail. The mechanical infusion device 12 of FIGS. 5A and 5B includeseveral of the components described and illustrated in U.S. Pat. Nos.4,202,333; 4,298,000; 4,430,079; and 4,597,754. The descriptions ofthese patents, including several of the components of the mechanicalinfusion device 12 described therein, are incorporated herein byreference. Moreover, such infusion devices are commercially availablefrom 3M Corporation and their product specification sheets are alsoincorporated by reference.

In those instances where the mechanical infusion device 12 is employedwithin the environment of the magnetic field, the infusion device 12should be fitted or manufactured with magnetic resonance compatiblematerial. For example, the infusion devices which are commerciallyavailable from 3M Corp., should be fitted with a magnetic resonancecompatible spring. This requires manufacturing the spring fromnon-magnetic materials, for example, plastic or certain metal alloyssuch as eljaloy or inconel.

To obtain a constant or variable rate of infusion of the magneticresonance contrast agent, the device 12 of FIGS. 5A and 5B may include aspring which has a constant width and thickness in order to exert aconstant force; or, alternatively, the spring may have a variable widthand/or variable thickness to provide a variable spring force. Under thiscircumstance, the infusion rate may be controlled to be either constantor variable by design of the spring and, in effect, pre-programmed byselection of the spring's design parameters.

In one preferred embodiment, the infusion device 12 may be designed toaccommodate a 50 cc syringe having a fluid capacity of 60 cc andcontaining one dose of the contrast agent. The infusion device 12 mayalso be designed to permit an external force on the syringe to modify orcustomize the rate of infusion of the contrast agent. This externalforce is separate from the force of the spring of the infusion device12.

Further, the infusion device 12 may include a flow rate indicator 50(FIG. 5B) to provide an indication of flow rate of the contrast agent tothe patient. Under this circumstance, the operator may visually oraudibly observe, in a rather simple manner, the rate of flow of thecontrast agent. This will allow the operator to exert an external forcemore accurately (both in the amount of force applied and in a timingsense) thereby facilitating a modification of the predeterminedinjection rate. Further, in an automated-type of infusion device, theflow rate indicator 50 permits the operator to visually or audiblymonitor a “pre-programmed” infusion rate or sequence.

Briefly, with reference to FIG. 5A, the mechanical infusion device 12further includes syringe 24, a syringe clamp 26, a syringe restraint orstop 28, a block and spring housing 30 a, roller bearings 30 b, a refluxvalve 32 and a catheter 34 having tubing 34 a and a needle 34 b(butterfly type). The syringe 24 contains the contrast agent to beadministered to the patient during magnetic resonance imaging. A plunger24 a of the syringe 24 is engaged by a spring 40 which is housed in theblock and spring housing 30 a. In operation, the spring 40 engages theplunger 24 a to pressurize the syringe 24. The syringe is maintained ina stationary position within the mechanical infusion device 12, and inparticular, in housing base 12 a, via the syringe clamp 26 and thesyringe restraint 28.

In one preferred embodiment, the mechanical infusion device 12 iscoupled to a saline drip apparatus 42 (saline drip 42 a, tubing 42 b androller clamp 42 c). The saline drip apparatus 42 is applied to an inputof a y-port connector 44. The syringe 24 is applied to the other inputof the y-port connector 44. This conventional configuration facilitatesa saline flush following the administration of the contrast agent withinthe syringe 24. In those instances where the tubing leading from thesaline drip apparatus 42 to the y-port connector 44 has a one-way valveto prevent reflux of contrast, it is acceptable to leave the saline drip“on” during infusion. Under this circumstance, as soon as the infusionof the contrast agent is complete, the drip infusion will automaticallyresume to “flush” gadolinium within the intravenous tubing and deliverthe contrast agent which remains in the tubing to the patient.

The rate of injection of the contrast agent from the syringe 24 isdetermined or controlled, in large part, by the size or gauge of theneedle 34 b, which functions as a fluid flow restrictor according toPoiseulle's Law. The rate of injection is also controlled by the amountof force that the spring 40 (the restoring force of the spring 40)applies to the plunger 24 a of syringe 24, the syringe cross-sectionalarea, the gadolinium viscosity as follows:${{Infusion}\quad {Rate}} = \frac{\pi \quad r^{4}F}{8\quad L\quad \mu \quad A}$

where: r=radius of flow restricting needle lumen;

F=spring force;

L=length of flow restricting needle;

μ=viscosity of the fluid; and

A=cross-sectional area of the syringe.

Examining the infusion rate equation immediately above reveals that avariation of the syringe size (A), needle length (L), and/or fluidviscosity (μ) impacts the rate of infusion of the contrast agent. Theviscosity of the fluid, however, may be dependent on the temperature ofthe contrast agent (gadolinium chelate). Thus, in those instances wherethe temperature of the contrast agent alters the viscosity of thecontrast, the rate of infusion is also dependent on this “variable.”

It should be noted, however, that the influence of viscosity on the flowrate may be substantially reduced by employing a fluid flow restrictorwhich minimizes the effects of viscosity on the rate of fluid flow.

In one embodiment, the characteristics of the spring 40 (e.g., springforce) may be selected or designed such that the spring 40 applies aconstant force upon plunger 24 a throughout the period of contrastinfusion. In another preferred embodiment, the characteristics of thespring 40 may be selected or designed such that the spring 40 applies avariable force on the plunger 24 a. That variable force may correlatewith the imaging process so that a maximum or substantially elevatedinjection rate provides a maximum or substantially elevatedconcentration of contrast in the artery of interest during thecollection of image data which corresponds to the center of k-space.

The rate of injection, however, may be increased or decreased using amanual, spring loaded, or pneumatic/electrical injection rate adjustmentmechanism which may be connected to various components of the device 12,including, the spring 40, the block and spring housing 30 a, the rollerbearings 30 b, the plunger 24 a, the tubing 34 a, and/or the fluid flowrestrictor 34 b. The pneumatic or electrical type injection ratemechanism may be coupled to the detection mechanism 110 which wouldpermit modification of the rate of injection. This embodiment isdescribed in detail below.

FIG. 5B illustrates a manual injection rate mechanism 50 for allowingthe operator to readily alter the rate of injection and thereby modifythe rate of injection of the contrast agent to accommodate or implementa desired timing of an elevated or maximum rate of flow of the contrastagent.

The spring force should be sufficient such that the flow restrictor,required to give the desired flow rate, has a flow resistance that ismuch greater than any flow resistance in the intravenous line. Thespring force should not be so high that a person of ordinary strengthcan not reduce or increase this force when a manual spring adjustmentmechanism 50 is designed as the means for adjusting the rate of flow(i.e., the amount of external force applied to the spring) of thecontrast agent. In general, a spring with about 5-10 pounds of springforce is suitable for 2-3 minute infusions and a higher spring force maybe required for faster infusions. Infusions as short as 30 seconds mayrequire a spring force of 20-30 pounds.

A fluid flow restrictor may be manufactured from, include or becomprised of a needle, a short piece of tubing of narrow calibre (e.g.,an intravenous angiocatheter of 20 gauge or larger may be satisfactory),an orifice (for example made of ruby or sapphire), a focal compressionof the IV tubing, or other mechanism which impedes the flow of fluid.

It should be noted that a precision orifice may offer several advantageswhen employed as a fluid flow restrictor. For example, in thoseinstances where an incompressible fluid is to be administered, such asgadopentetate dimeglumine, gadoteridol, or gadodiamide, flow through anorifice is governed by the Bernoulli effect. In this regard, the flowrate of the fluid through the orifice is proportional to the square rootof the pressure drop:${{Infusion}\quad {Rate}} = {K*\sqrt{\left( \frac{F}{A} \right)}}$

where: K=a constant determined by the geometry of the orifice;

F=spring force; and

A=syringe cross-sectional area.

Further, it should be noted that the pressure drop across an orifice isgoverned by inertial effects of the fluid; the viscosity of the fluidhas little to no impact. As a result, an orifice minimizes the influenceof the viscosity of the fluid on the rate of flow of the fluid. Underthis circumstance, by using an orifice as a fluid flow restrictor, theBernoulli effect predicts the same flow rate regardless of temperatureof the fluid and regardless of which gadolinium compound is employed.Although in practice it is essentially impossible to entirely eliminateviscosity effects of the fluid, those effect are markedly reduced.

TABLE 1 provides the infusion rate, with respect to three MR contrastagents, for a variety of needles and flow restricting orifices whenemployed in an infusion device 12 substantially as illustrated in FIG.5A where the spring 40 is a 6 pound-force spring and the syringe 24 is a1 inch diameter, 50 cc syringe.

In those instances where the rate of flow of the fluid is dependent onthe ambient temperature or the temperature of the contrast agent,consistent operation of the infusion device 12 may require either atemperature controlled operating environment or use of a fluid flowrestrictor whose operational characteristics are essentially unaffectedby the viscosity of the fluid (e.g., a precision orifice).

With reference to FIG. 5B, in one embodiment, the rate adjustmentmechanism 50 is a manual type including a lever 50 a by which the usermay increase or decrease the force applied to the plunger 24 a. Thelever 50 a engages the plunger 24 a and spring 40 so that the resultingforce applied to the plunger 24 a is essentially determined by the sumof the force applied to the plunger 24 a (i.e., by the lever 50 a) andthe spring force, F. By employing this configuration, the user mayincrease or decrease the rate of injection at a particular moment of theimaging sequence. For example, increasing the infusion rate at about 10to about 40 seconds prior to the acquisition of image data correspondingto the center of the k-space would cause an elevated, substantiallyelevated or relatively high arterial gadolinium level to be maintainedin the artery of interest during acquisition of image data correspondingto the center of k-space (typically it takes about 10-40 seconds forvenous blood in the arm to circulate through the heart and lungs toreach the artery of interest). Such a technique may provide additionalcontrast enhancement of the image of the artery relative to veins andsurrounding tissue.

It should be noted that the center of k-space may be characterized as10% to 75% of the total k-space data which corresponds to the lowestspatial frequency information.

It should be further noted that a substantially elevated concentrationof the contrast agent in the arterial blood may be described as aconcentration which is greater than 2.9/seconds-relaxivity (of thecontrast). As mentioned above, a substantially elevated rate of infusionprovides a substantially elevated concentration of the contrast agent inthe artery of interest.

The infusion device 12 of FIG. 5B further includes a flow rate indicator52 to provide the operator an indication of a flow rate (injection rate)of the contrast agent to the patient. Here, the operator may visually oraudibly observe the rate of flow of the contrast agent to therebyaccurately control the rate of injection of the contrast agent into thepatient; the operator may customize or modify the contrast injectionrate.

The flow rate indicator may be implemented using an optical type sensorfor sensing the linear motion of, for example, the plunger 24 a, thespring 40, and/or the block and spring housing 30 a, or the rotationalmotion of the roller bearings 30 b. Such a mechanism permits an accuratemeasurement with little to no impact on the operation of the injectiondevice 12, including the motion of the plunger 24 a and the operation ofthe spring 40. That is, an optical type rate indicator has an advantageof not requiring physical contact with the contrast agent in the syringe24 or spring 40.

It is noted, however, that a fluid flow or motion sensor may also beemployed in the flow rate indicator 50. Such devices provide accurateinformation regarding the rate of flow of the contrast agent in thesyringe 24 or in the tubing 34 a.

As mentioned above, when the mechanical infusion device 12 is employedwithin the environment of the magnetic field, the materials used tofabricate the device 12 should be non-magnetic. That is, magneticmaterials should be avoided when the device 12 is implemented in or nearthe magnetic field of the magnetic resonance imaging apparatus. In thoseinstances, the spring 40 (FIGS. 5A and 5B) should be manufactured fromnon-magnetic materials, for example, eljaloy or inconel.

With reference to FIGS. 6A-C, the mechanical infusion device 12 may beimplemented using a bag-cassette configuration. The bag 46 contains acontrast agent. Analogous to the syringe configuration of FIGS. 5A and5B, the bag 46 may be placed into a cassette 48 which applies evenpressure over the contact surface of the bag 46. In operation, thecontrast agent then flows, similar to the syringe 24, from the bag,through the catheter 34 to the patient. As with the case with thesyringe configuration, fluid flow control is provided by means of afluid flow restrictor (i.e., the needle 34 b) used in combination with acassette 48 which provides the force.

It should be noted that. the bag-cassette arrangement of FIGS. 6A-C mayemploy a saline drip apparatus 42 as well as a rate adjustment mechanism50. As with the syringe configuration, the rate of injection may beincreased or decreased using a manual, spring loaded, or electrical orpneumatic rate adjustment mechanism.

In some magnetic resonance suites, an opening exists in the walldividing the magnet of the imaging apparatus and the control equipment(i.e., computer and other electronic devices). In these situations,standard infusion pumps (containing metal, magnetized material andelectronic circuits) can be used from outside of the MR suite toimplement the methods described herein.

In one preferred embodiment, a pump manufactured by Abbott, the LifeCare 5000, may be implemented. The Life Care 5000 draws drugs (e.g.,contrast agent) directly from a bottle and preloads it into a longlength of tubing. The operating parameters of the Life Care 5000 may bepreprogrammed to execute numerous infusion rates.

In another preferred embodiment, the injection rate for contrast ismatched with the mapping of k-space so that a maximum or substantiallyelevated arterial gadolinium concentration correlates with acquisitionof image data corresponding to the center of k-space. That is, theoperating parameters of the pump may be pre-programmed to provide aninjection rate for contrast agent which is matched with the mapping ofk-space so that a maximum or substantially elevated rate of infusionoccurs about 10-40 seconds prior to the collection of image datacorresponding to the center of k-space.

The operating parameters of the pump may also be controlled by thedetection system 110 (as described below). The timing of a maximum,elevated or substantially elevated rate of injection may be controlledby the detection system 110 in order to more accurately synchronize thecollection of image data which is representative of the center ofk-space to a maximum, elevated or substantially elevated concentrationof contrast in the artery of interest. This embodiment is discussed inmore detail below.

This type of configuration offers several advantages including: (1) thecontrast agent (gadolinium) need not be removed from its shippingcontainers into an intermediate container, for example, a syringe; (2)the programmability of the pump allows variable injection ratesproviding for a maximum rate at the peak when the center of k-space isbeing mapped (which may be the most critical period during imageacquisition); (3) operator control of the operating parameters.Moreover, the Life Care 5000 may be coupled to the detection system 110to facilitate the mapping of k-space by the imaging system 16 with thearterial phase of contrast enhancement in the region of interest.

It should be noted that the Life Care 5000 Pump may not be ideallysuited for implementing all of the techniques described herein. Forexample, such deficiencies include the rates of injection of the pump,the degree of programmability of the flow delivery characteristics ofthe pump, and allowing the pump to administer contrast from multiplecontainers which will permit multiple 20 cc vials to be used.

When implementing longer pulse sequences (greater than 2 minutes) orpulse sequences which collect image data representative of the center ofk-space some time after initiation of image data collection, it isimportant that no contrast be administered prior to magnetic resonancescan since the contrast may leak into the background tissues and cause adegradation of the image. If some paramagnetic contrast or othermagnetic resonance contrast has been administered prior to imaging, itmay be useful to delay the arterial scan until this contrast has beenexcreted by the patient, in order to increase the probability ofobtaining optimal images.

An exception to this requirement is when a small test dose of contrastor the like (sodium dehydrocholate, saccharin or indocyanine green) isused to determine the circulation time prior to performing the dynamicinjection with imaging. By infusing a small test dose of a fewmilliliters and then imaging rapidly the region of interest, it ispossible to determine the time interval between contrast infusion andcontrast arrival in the artery. This time may then be used to guidetiming for the image acquisition in that it may facilitate more accuratecorrelation between the injection of the contrast agent and theacquisition of the data representative of the center of k-space when theimaging system 16 collects such data in the middle of the scanningsequence. Thus, this time should roughly equal the time between themiddle of the infusion and the moment of acquisition of the center ofk-space for short infusions.

In those instances where the imaging apparatus employs pulse sequenceshaving very short data acquisition periods the contrast agent may beinjected before the initiation of collecting image data. Short pulsesequences may be characterized as those sequences for which the timerequired for contrast to circulate from injection site to the artery ofinterest becomes a significant fraction of the imaging time, forexample, data acquisition periods of less than 2 minutes. Under thiscircumstance, injection of the contrast agent before acquisition ofimage data is necessary to allow circulation of the contrast agent inthe patient and thereby correlate a maximum or substantially elevatedarterial concentration with the collection of image data representingthe center of k-space. Administering the contrast agent prior to theacquisition of image data would cause a relatively high arterialgadolinium level during the mapping of k-space. As discussed above, therelative timing between the administration of the contrast agent and thecollection of image data representing the center of k-space should beadapted to account for the injection mechanism employed, the location ofthe artery of interest, the size of the artery of interest, and thephysical condition of the patient. For example, the contrast may beadministered about 10-40 seconds before collection of image data toaccount for venous blood in the arm to circulate through the heart andlungs to reach the artery of interest. Thus, the amount of time beforeacquisition of image data may depend on the configuration of thecontrast delivery mechanism, the relative location of the artery ofinterest, the relative size of the artery of interest, and the conditionof the patient, including the age of the patient. Employing theseconsiderations in selecting and controlling the timing of the injectionprovide a more accurate alignment between the acquisition of datarepresentative of the center of k-space and a period of maximum orsubstantially elevated contrast concentration in the artery of interestrelative to adjacent veins.

When employing the conventional imaging sequence which maps k-space inthe middle of the scan, in a preferred embodiment, a constant infusionshould begin within a few seconds of initiation of the scan process. Thecontrast infusion should end about 20 or more seconds before thecompletion of the scan; this allows the intravenously injected contrastto circulate through the heart and into the arteries. A chaser of normalsaline or other fluid may be used to insure injection of the entire doseof the paramagnetic contrast (e.g., gadolinium) and, in addition, toinsure that there is sufficient venous return to propel the injectedcontrast to the heart. In a preferred embodiment, the contrast infusionrate is matched with the mapping of k-space so that the maximum arterialgadolinium concentration occurs during acquisition of the center ofk-space. This may permit injecting over a shorter period of time toachieve either a higher injection rate or a lower contrast dose.

In one preferred embodiment, the magnetic resonance contrast agent isinjected by the infusion device 12 in a bolus manner and the imagingsequence, implemented by the imaging system 16, collects data which isrepresentative of the center of k-space at or near the beginning of thesequence. Under this circumstance, in order to correlate, on arepeatable basis, a maximum, elevated or substantially elevated arterialconcentration of the contrast agent in the artery of interest with thecollection of image data corresponding to the center of k-space, thedetection system 110 monitors or measures the response from the regionof interest to detect the arrival of the contrast agent in that region.Upon detecting the arrival of the contrast agent in the region ofinterest, the imaging system 16 may initiate collection of image datarepresentative of the center of k-space. The center of k-spacecorresponds to the low spatial frequency data which dominates imagecontrast.

In a preferred embodiment, the period of a maximum or substantiallyelevated rate of infusion of the magnetic resonance contrast agent tothe patient is adapted according to the size of the artery of interestin order to correlate with the period of the collection of image datacorresponding to the center of k-space to the period of the arterialphase of contrast enhancement. In this regard, where the artery ofinterest is relatively large (e.g., the aorta), a period of asubstantially elevated or maximum injection rate may overlap for asmaller fraction of the total image time than where the artery isrelatively small (e.g., renal). For example, when imaging largerarteries, the administration of the contrast agent may include a periodof a substantially elevated or maximum rate of contrast which provides asubstantially elevated or maximum arterial concentration for less than50% of the period during which the system collects image datacorresponding to the center of k-space; and preferably between 20% to50%. Where the artery of interest is relatively small, it is preferablethat a period of maximum or substantially elevated rate of injectionprovide a maximum or substantially elevated concentration of thecontrast in the artery of interest for more than 50% of the period ofmapping the center of k-space; and preferably between 50% to 85%.

With reference to FIG. 7, the infusion of the magnetic resonancecontrast agent may be by way of manual means. In this embodiment, asyringe 20, having needle 22, is coupled to a vessel 18 containing themagnetic resonance contrast agent. The vessel 18 is coupled to thepatient using conventional techniques, for example, appropriatelyselected tubing 14 which permits fluid flow between the vessel 18 andthe patient, for example, an angiocatheter.

When injecting the contrast agent using a manual injector, i.e.,injecting the magnetic resonance contrast agent by hand, during themagnetic resonance angiography sequences, in a preferred embodiment, theinfusion “path” includes a fluid flow restrictor which adds resistanceto the flow of gadolinium during administration into the body. It shouldbe noted that a fluid flow restrictor may be, for example, a standardinjection needle or small calibre angiocatheter. In FIG. 7, the fluidflow restrictor may be the needle 22 of syringe 20 and/or theangiocatheter 14. Use of small needles, short pieces of tubing of narrowcalibre, an orifice, and/or small calibre angiocatheters may alleviateerrors of injecting the contrast too rapidly and, as a result, depletingor running-out of contrast too early in the scan or improperlycorrelating a maximum or elevated rate of infusion with the mapping ofk-space. In a preferred embodiment, the needle size may be 22 gauge orsmaller diameter (higher than or equal to 22 gauge) depending upon theviscosity of the contrast agent for an infusion of 2-4 minutes.Angiocatheter of 20 gauge may be suitable for infusions of about 30seconds.

It may be convenient to pre-load the entire dose of contrast into avessel or length of tubing with luer lock or other appropriateconnectors at each end of the tubing. It is then possible to use asingle saline filled syringe to inject the contrast followed by a salinechaser without having to switch syringes or pumps. Saline is a preferredfluid to use as a chaser since it can be made isotonic with blood and iscompatible with most intravenous fluids and pharmaceuticals that mayalready be flowing through a patient's IV line.

In a preferred embodiment, the contrast is infused slowly at thebeginning and fastest near (about 10-50 seconds before) the middle ofthe acquisition. This type of injection pattern, based upon the factthat the contrast does somewhat contribute to venous and backgroundtissue enhancement, avoids excessive contrast early in the acquisition.

In another preferred embodiment, the magnetic resonance contrast agentis injected rapidly in a bolus manner and the imaging sequenceimplemented by the imaging system 16 collects image data which isrepresentative of the center of k-space at or near the beginning of thesequence. Upon detecting the arrival of the contrast agent in the regionof interest (by the operator or detection system 110), the imagingsystem 16 may initiate the imaging sequence and collection of image datarepresentative of the center of k-space.

Another embodiment of a manual infusion means is illustrated in FIG. 13.In this embodiment, a syringe 20 is loaded with a magnetic resonancecontrast agent. A 3-way stopcock 44 permits rapid contrast agent (e.g.,gadolinium) injection without risk of retrograde flow. Another side portof the stopcock 44, further from the patient, accommodates an additionalsyringe 20′ which may be employed as a rapid saline flush immediatelyfollowing the contrast injection.

A drip chamber 42 d allows the operator to observe that the tubing 14 isintravascular and working properly. In this regard, a bag of normalsaline 42 a, or other suitable fluid, is connected to the proximal endof the tubing 14 via a drip chamber 42 d. The operator may observe thedrip chamber 42 d to determine whether the intravenous line is workingproperly. A roller clamp 42 c may be employed to prevent too rapidsaline flow into the patient.

It should be noted that a bag of saline 42 a which is too large may beharmful to the patient should the entire volume of saline beadministered to the patient; using a small bag of saline, accidentaladministration of the entire bag will not be harmful. Typically, a 250cc bag of fluid is suitable for providing enough fluid to last for theentire exam and to avoid injury to the patient if there is accidentalrelease of the entire quantity of the fluid into the circulation in ashort span of time (e.g., in less than 15 minutes).

The dynamic infusion of contrast may be facilitated by using tubing 14which reaches inside the magnet and which allows the operator infusingcontrast to stand comfortably outside the magnet environment where it ispossible to watch a clock and/or have access to control panels for theimaging system 16 to initiate the scan. With a sufficient length oftubing, the operator may comfortably use both hands to perform theinfusion; generally one hand holds the syringe plunger and the otherhand holds the syringe chamber.

In those embodiments where the operator is positioned outside the magnetenvironment, at least 4 to 6 feet of tubing may be required to reachoutside the magnet environment. A side port for gadolinium infusionshould be located about 4 to 7 feet away from the end of the tubingwhich is at the intravenous puncture site. A second side port a fewinches further away is also useful to allow sufficient space for bothgadolinium filled and saline filled syringes to be attachedsimultaneously. This allows the gadolinium infusion to be immediatelyfollowed with the saline flush without any delay for switching syringes.By placing one-way valves in the tubing upstream from each side port,the fluids (contrast agent and flush) are forced to flow in the correctdirection without risk of retrograde flow in the tubing. One of theone-way valves should be between the two side ports so that the contrastagent may not “backup” into the other syringe used for flush. This isparticularly important when the gadolinium is injected so rapidly that ahigh infusion pressure is required. The most proximal one-way valvecould be replaced with a clamp or other mechanism to impede flow.

It may also be useful to have an extra port (a third port) positionedclose to the distal end of the tubing where it attaches to the patient.This port can be used for treating any reaction that the patient mighthave to the contrast being infused. By having this third port close tothe patient, it minimizes the distance that medicines must travel inorder to reach the patient's circulation. It is anticipated that in theevent of a contrast reaction, the patient would be immediately removedfrom the magnet so that this third port would be readily accessible.

Proximal and distal ends of the tubing should have standard medical typeluer locking connectors. The distal end should have a male connector. Itis useful if this distal end has a locking mechanism to prevent thetubing from becoming detached from the intravenous catheter during theincrease pressure of fast infusions. A flow meter that provides feedbackto the operator about the contrast infusion rate may be useful.

The inner diameter of the tubing 14 may be important. The tubing's innerdiameter may be selected to strike a balance between a sufficientdiameter to minimize flow resistance but not so large a diameter thatthere is a large dead space. Dead space is the volume of tubing betweenthe IV site in the patient's arm and the point where the syringe 20attaches to the tubing 14.

In one embodiment, a tubing inner diameter of about 0.08 inch strikes agood balance between the need to minimize resistance and the need tominimize dead space for tubing that is about 6 feet long withgadopentetate dimeglumine or gadodiamide as contrast agents. The tubing14 may be made of plastic, rubber or any other suitable (non-magnetic)material. The tubing 14 should be pliable so that it can easily adjustor conform to the path of the intravenous site on the patient's arm tooutside the magnet environment. In some situations it is also useful ifthe tubing assumes a natural coil configuration so that it will tend tostay wound up. This helps to avoid having the intravenous tubingbecoming intertwined with other tubing or wires in the general vicinityof the magnet and imaging system 16.

Detection System

The detection system 110 detects the concentration of contrast agent inthe region of interest; and, more particularly, detects the “arrival” ofcontrast in the region of interest as well as detects the concentrationof contrast therein. In addition, the detection system 110 may be usedto precisely synchronize the collection of a predetermined portion ofimage data (e.g., center of k-space) by the imaging system 16 with thearterial phase of contrast enhancement of the region of interest (arteryand tissues in the region of interest).

The detection system 110, in conjunction with the imaging system 16,monitors and detects the relative concentration of the contrast agent inthe region of interest by comparing the response of a region of interestbefore the administration of magnetic resonance contrast agent to thepatient to the response of the region of interest during and/or afteradministration of the contrast agent. When a characteristic change inthe response to the magnetic resonance pulse is measured by thedetection system 110, the imaging system 16 begins collecting image datawhich is representative of the center of k-space.

In operation, prior to administration of contrast agent to the patientand before initiation of the imaging sequence, the detection system 110initially measures the response from the region of interest to a seriesof pulses form the imaging system 16. Here, the detection system 110acquires a response from the region of interest before administration ofcontrast agent. This response may be described as a base line orpre-contrast response.

After the base line or pre-contrast response is measured, the contrastagent may be administered to the patient. The detection system 110 maythen measure the response from the region of interest to a series ofmagnetic resonance pulses from the imaging system 16. The detectionsystem 110 or the operator may evaluate the response from the region ofinterest to determine a characteristic change in the response from theregion of interest. This characteristic response may indicate thearrival of contrast in the region of interest or the onset of thearterial phase of contrast enhancement.

The subsequent operations of the detection system 110 depends somewhaton the parameters of injection rate of the injection system 12 and thedata collection techniques and configuration of the imaging system 16.In this regard, in those instances where the injection of the contrastagent is of a bolus type (i.e., rapid injection rate), thecharacteristic change in the response to the magnetic resonance pulsesmay indicate that the region of interest is in or is “entering” thearterial phase of the magnetic resonance contrast enhancement. Underthis circumstance, the detection system 110 instructs the imaging system16 to initiate an imaging sequence. The imaging system 16, immediatelyor shortly thereafter, collects the predetermined image data of theimaging sequence (e.g., center of k-space).

It may be useful to have a short delay between detecting the arrival ofcontrast in the arteries of interest and beginning collecting datarepresentative of the center of k-space. This delay may allow thecontrast to reach all of the arteries throughout the entire imagingvolume (region of interest).

In another embodiment, the imaging system 16 repeatedly collects datarepresentative of the center of k-space before and during arrival of thecontrast in the imaging volume. The remaining portions of k-space data(i.e., the periphery of k-space) may be collected either before or aftercontrast arrives in the imaging volume. It may then be possible toreconstruct a series of images showing the temporal pattern of contrastarriving in the imaging volume. In this embodiment, a detection system110 may not be necessary.

In the alternative, however, the detection system 110 may detect whencontrast has arrived in the imaging volume so that one or only a fewmore sets of data representative of the center of k-space need beacquired before switching to acquiring data representative of theremaining portion of k-space (i.e the periphery of k-space). In thisembodiment, it may be useful if the data representative of the center ofk-space corresponds to a small fraction of the total k-space data (i.e.10-30%) so that it may be repeatedly collected in a short period of timefor high temporal resolution of the vascular and tissue enhancement.

Where the predetermined image data is data which is representative ofthe center of k-space, the magnetic resonance imaging pulse sequenceshould be arranged such that the central portion of k-space data iscollected in the beginning or near the beginning of the sequence. Theperiphery of k-space may be collected thereafter. Under thiscircumstance, the detection system 110 provides precise synchronizationbetween the arterial phase of contrast enhancement and the collection ofimage data which is representative of the center of k-space.

Where the magnetic resonance pulse sequence collects data which isrepresentative of the center of k-space in the middle of the scan (aconventional type scan), the detection system 110 may be employed todetermine an “adjustment” of the infusion rate of the contrast agent bythe infusion device 12 so that a period of maximum, elevated orsubstantially elevated concentration of contrast agent in the region ofinterest is correlated to the collection of image data which isrepresentative of the center of k-space (i.e., mapping of k-space). Asnoted in the related applications, the time between contrast injectionand a maximum or substantially elevated contrast concentration in theartery of interest may vary according to a number of factors includingthe location of the artery of interest, the size of the artery ofinterest, the physical condition of the patient, and the time delay dueto the configuration of the infusion system 10. In this embodiment, thedetection system 110 may be employed to automatically adjust the rate ofinfusion of the infusion device 12 so that the imaging sequence collectsa sufficient amount of data which is representative of k-space duringthe arterial phase of the enhancement of the region of interest.

In this embodiment, the detection system 110 monitors the response ofthe region of interest to series of magnetic resonance detection pulses.When the detection system 110 determines that the contrast has “entered”the region of interest, the detection system 110 may adjust the rate ofinjection of the contrast agent to alter the timing of the arterialphase of contrast enhancement.

The detection system 110 may calculate an adjustment to the rate ofinfusion based on several factors including the circulation time delayof the contrast agent, the timing of the mapping of k-space, and thecurrent and future rates of infusion. The detection system 110 may thenincrease or decrease the rate of injection by the infusion device 12accordingly to provide sufficient or maximum overlap between the mappingof k-space and the arterial phase of contrast enhancement.

As mentioned above, the detection system 110 may detect theconcentration of the contrast in the region of interest in a number ofdifferent ways including, for example, a change in the amplitude of theresponsive radio frequency signal.

In one embodiment, the monitoring and evaluating operations of thedetection system 110 and the imaging system 16 is initiated only whenthe contrast agent is expected in the region of interest. In thisregard, the application of the detection pulses employed todetect/monitor the “arrival” of the contrast agent to the region ofinterest, may be delayed from the infusion of the contrast in an amountrelated to the time delay due to the infusion system 10 and thetime-delay due to the time required for the contrast agent to circulatefrom the site of injection, through the body, and into the artery ofinterest. This will confine the use of the magnetic resonance imagingsystem 16 and detection system 110 to the period when the maximum,elevated or substantially elevated contrast concentration isanticipated.

FIG. 12 illustrates the detection system 110 of the present invention.In this embodiment, the detection system 110 includes a microcontroller112 and a signal analyzer 114 (e.g., an oscilloscope). Themicrocontroller 112 (which includes an adequate supply of memory) isprogrammed to calculate the base line or pre-contrast signal responsefrom the region of interest prior to the administration of the contrastagent as well as the concentration of the contrast agent in the regionof interest after administration of the contrast agent. Themicrocontroller 112 acquires an electrical representation of the signalresponse from the signal analyzer 114. In response, the microcontroller112 calculates the base lines response and the contrast concentration inthe region of interest.

In one embodiment, the detection system 110 controls the imaging system16. In this regard, the detection system 110 instructs the imagingsystem 16 to initiate a predetermined imaging sequence at an appropriatetime depending on detecting a characteristic change in the signalresponse from the region of interest, as described above. Themicrocontroller 112 couples to the imaging system 16 via electrical oroptical coupling mechanism 112 a.

In another embodiment, the microcontroller 112 includes an operatorinterface which allows the operator to observe the response measured bythe signal analyzer 114. In this embodiment, the microcontroller 112facilitates the operator's observation and analysis of response signalsincluding assessing the concentration of contrast in the region ofinterest. The microcontroller 112 may include a visual and/or audibleindicator to indicate the onset of the arterial phase of contrastenhancement or to indicate the concentration of contrast agent in theartery of interest. Such a configuration would facilitatesynchronization between the collection of image data which isrepresentative of the center of k-space with the arterial phase ofcontrast enhancement.

It should be noted that the operator may observe the signal measured bythe signal analyzer 114 in addition to or in lieu of the operatorinterface of the microcontroller 112. Under this circumstance, themicrocontroller 112 may be unnecessary.

In another embodiment, the microcontroller 112 controls the rate ofinfusion by the infusion system 10 (e.g., mechanical pump 12, Life Care5000 and/or the size of the orifice of the fluid flow restrictor).Similar to the control of the imaging system 16, the microcontroller 112(which is appropriately programmed) may adjust the rate of infusion tocorrelate the collection of image data which is representative of thecenter of k-space with a maximum, elevated, or substantially elevatedconcentration of contrast agent in the region of interest. Themicrocontroller 112 may adjust the rate of injection via controlling theinfusion adjustment mechanism on the infusion device 12 (see, FIGS. 5Aand 5B). The microcontroller couples to the infusion system 10 viaelectrical, optical, or pneumatic coupling mechanism 112 b.

As mentioned above, the detection system 110 may compute an adjustmentto the infusion parameters or sequence of infusion system 10 based onseveral factors including the circulation time delay, the relativetiming of the mapping of k-space, and pre-programmed rate of infusion.The detection system 110 may then increase or decrease the rate ofinjection by the infusion device 12, via the infusion adjustmentmechanism, to provide a period of arterial phase of contrast enhancementwhich extends during the collection of image data which isrepresentative of the center of k-space.

Appendage Cushions

One important detail relates to the positioning of the arms duringscanning. By placing appendage cushions 120 a and 120 b along eitherside of the patient's torso (see FIGS. 13A and 13B), the arms areelevated or lifted up in the air. This has several important effects.First, by lifting the arms, the intravenous site of contrast agentinjection is elevated thereby creating a “down hill” path for thecontrast agent which assists venous return. Under this circumstance, thecontrast agent more rapidly enters the central veins to achieve a fasterand more predictable circulation time. The circulation time is the timerequired for contrast agent (e.g., gadolinium) to circulate from thesite of infusion through the body to the artery(ies) of interest.

An additional advantage of employing the appendage cushions 120 a and120 b is that such an arrangement prevents the arms or other stuff fromgetting into the region along side the patient where it could result inaliasing (wrap-around artifact) when the imaging the torso with acoronally oriented volume.

In one embodiment, the cushions 120 a and 120 b may be made of foam orother material that has a low density of hydrogen nuclei. This is toensure that the cushions 120 a and 120 b do not create much signal ornoise during imaging. The length of the cushions 120 a and 120 b shouldbe long enough to keep the arms up along the entire length of the torso.It may be useful in patients with wide hips and narrow torsos to makethe cushion thinner in the region of the hips. Alternatively, thecushions may be short enough so that it comes down to the hips but doesnot overlap the hips.

In a preferred embodiment, the appendage cushions 120 a and 120 b are 8cm thick of non-magnetic material, low density material. The appendagecushions 120 a and 120 b may be rectangular in shape and may be securedto the patient or the imaging apparatus prior to imaging using anon-magnetic strapping mechanism, for example, a velcro strap or similarmaterial/mechanism. The surfaces 122 a and 122 b of the appendagecushions 120 a and 120 b may be shaped in a conformal nature to that ofthe patient's body. This shape provides for a more stable configurationso that there is little to no movement of the appendage cushions 120 aand 120 b relative to the patient.

Further, the upper surfaces 122 a and 122 b of the appendage cushions120 a and 120 b may be sloped downward in the direction towards thepatient. This shape allows the arms, when in a relaxed state, to rest inthe corner of the torso and the upper surfaces of the appendage cushions120 a and 120 b which minimizes movement of the arms of the patientduring imaging.

Post-Processing

Post-processing of the scan data may be used. Maximum intensityprojection (MIP) collapse images are useful for rapidly examining theentire arterial circulation within the region of interest. It may beuseful to reformat and selectively collapse the data through thespecific arteries of interest. Additional contrast may be obtained bydigitally subtracting a pre-gadolinium acquisition from the dynamicgadolinium acquisition. Volume rendering and surface rendering may alsobe useful and is possible with these high contrast volume data sets.

Additional Sequences

After performing a dynamic contrast enhanced scan, it is possible toobtain additional MR angiogram images in which there is enhancement ofboth arteries and veins, as well as liver, spleen, kidney, and otherorgans. Phase contrast magnetic resonance angiography is also improvedfollowing the administration of magnetic resonance contrast. It may thenbe possible to combine a dynamically enhanced scan for visualization ofprimarily the arteries with one or more post-gadolinium (contrast agent)scans to resolve anatomic or physiological issues that may be importantto a patient's condition.

Immediately below are examples of results obtained from use of preferredembodiments of the present invention. The parameters of the examples aredetailed therein.

EXAMPLE 1

Contrast between peripheral arteries and veins in images obtained byimaging dynamically during the administration of gadopentetatedimeglumine was investigated in sixteen patients referred foraorta-iliac magnetic resonance arteriography. These included 9 males and7 females with a mean age of 72 ranging from 67 to 83. The indicationsfor the study included hypertension (6), abdominal aortic aneurysm (AAA,6) claudication (4) and renal failure (9). Some patients had more thanone indication.

Parameters:

All imaging was performed on a 1.5 Tesla superconducting magnet (GeneralElectric Medical Systems, Milwaukee, Wis.) using the body coil andversion 4.7 or higher software. A 3D FT, coronal, spoiled, gradient echovolume was acquired centered on the mid-abdomen. The imaging parametersincluded: 12 cm volume with 60 partitions, 2 mm partition thickness, TRof 25 msec, a TE of 6.9 msec, a flip angle of 40°, first order flowcompensation, 36 centimeters field of view, 256 by 192 matrix. Theimaging time was 5 minutes and 10 seconds. Frequency was set superior toinferior so that phase artifact from diaphragmatic and cardiac motionwould not superimpose on the abdominal aorta and IVC. When possible,phase artifact noise was minimized by excluding the heart and lungsentirely from the field of view. No saturation pulses were employed. Thevolume data were reformatted through vessels of interest and alsodisplayed as maximum intensity projections.

Gadopentetate Dimeglumine Injection:

After pre-scanning, venous access was obtained via a 22 gaugeangiocatheter. A dynamic acquisition was then performed during handinjection of gadopentetate dimeglumine (Berlex Laboratories, CedarKnoll, N.J.), 0.2 millimoles/kilogram. The injection was initiatedwithin 5 seconds of initiating the image acquisition. The injection ratewas constant (within the limitations of a hand injection) and timed tolast until 10-20 seconds before completion of the scan. The injectionincluded a 5 cc normal saline chaser to ensure injection of the entiregadopentetate dimeglumine dose. As a result, the gadopentetatedimeglumine ended approximately 30-40 seconds before completion of thescan and the saline chaser ended about 10-20 seconds before completionof the scan. In order to compare to the conventional, non-dynamic,gadolinium-enhanced MRA, a second, identical acquisition was thenacquired without altering the imaging or prescan parameters.

Signal Measurements:

Signal intensity was measured in the abdominal aorta, IVC, iliac arteryand vein, renal artery and vein, celiac trunk, SMA, portal vein, hepaticvein and background tissue (including fat, skeletal muscle, kidney,liver and spleen) for 7 regions of interest per measurement. As many ofthese measurements as possible were obtained from the central 20partitions and all measurements were obtained from the central 40partitions. Identical regions of interest were used to compare vesselson the dynamic and post-gadolinium images. The standard deviation of theaorta signal was recorded as noise. Differences in the aorta and IVCsignal-to-noise ratio were evaluated for each patient as well as for themeans of all patients with Students t-test. In addition, thesignificance of differences in the mean portal vein, hepatic vein, renalvein and iliac vein signal compared to the IVC were evaluated withStudents t-test. The presence of aneurysms, occlusions and stenoses(>50%) was noted on the individual dynamic images and on maximumintensity projections and compared to findings at surgery orarteriography when available.

Results:

All sixteen patients tolerated the imaging and gadopentetate dimegluminewell; there were no complications. FIGS. 8A-C illustrate the typicalimages obtained before, during and after injection of gadopentetatedimeglumine, respectively. Before the injection, the vessels wereheavily saturated with only a few streaks of vessels visible at theedges of the 3D volume. Images obtained during injection showedenhancement of the arteries while the IVC remained indistinguishablefrom the background tissue. Aorta IVC signal intensity ratios, shown inTABLE 2, confirmed this preferential arterial enhancement in everypatient studied. Images obtained after the injection was completeddemonstrated comparable enhancement of both arteries and veins.

It should be noted that with dynamic imaging there is bright arterial aswell as portal vein and splenic vein enhancement but no visible IVC oriliac vein enhancement and no in-plane saturation. Post gadopentetatedimeglumine images show comparable enhancement of both arteries andveins.

TABLE 3 provides the average signal intensity for all tissues studiedfor both the dynamic and post-injection sequences. With dynamicgadopentetate dimeglumine the average aorta signal-to-noise ratio was10±0.9 compared to 5.1±1.4 in the IVC (p value≦0.0001), while postgadopentetate dimeglumine the aorta and IVC were nearly identical,10±1.4 and 9.5±1.3 respectively. Although all veins were less brightthan the aorta on the dynamic images compared to post gadopentetatedimeglumine images, there were variations among the veins analyzed. Theiliac vein was the least enhanced, 4.7±1.6, while the portal vein wasthe brightest, 8.3±1.6 followed by the hepatic, 7.5±2.1, and renal,6.2±1.8, veins; these differences were significant to the p<0.01 levelcompared to the mean IVC signal-to-noise ratio.

Angiographic and/or surgical correlation was available in 6 of the 16patients. In the vascular segments for which definitive correlation wasavailable, magnetic resonance arteriography correctly identified 2occlusions (1 common iliac and 1 renal artery), 10 stenoses (4 renalartery, 2 iliac artery, 2 distal aorta, 1 inferior mesenteric artery and1 celiac) and 6 aneurysms (3 aortic and 3 iliac artery). There was noevidence of arterial in-plane saturation in any patient. In one patientwith a common iliac artery occlusion, there was no difficultyvisualizing reconstituted flow distal to the occlusion.

TABLE 4 reveals an apparent trend for patients with a history of cardiacdisease, claudication or aneurysms to have the greatest aorta/IVC signalintensity ratio. The sample size may have been too small to establishstatistically significant correlations. Further, one patient withcardiac disease, aneurysmal disease and claudication had the highestaorta/IVC signal intensity ratio. These trends are opposite fromtime-of-flight imaging where cardiac disease and aneurysms areassociated with image degradation.

EXAMPLE 2

In order to determine the optimal timing of contrast administration, twomethods of dynamic administration, bolus and continuous infusion, werecompared to non-dynamic injections and to conventional time-of-flightimaging.

Gadolinium enhanced magnetic resonance arteriography was performed in 52patients referred for routine MRA of the abdominal aorta or branchvessels. Imaging was performed as described in Example 1. The totalacquisition time was 5:08 minutes to cover approximately 36 cm of aortaand iliac artery in the superior to inferior dimension. In 20 of thesepatients, the dynamic gadolinium infusion imaging was performed with 28partitions each 2 mm thick with a 256 by 256 matrix to reduce the scantime to 3:18 minutes.

After pre-scanning, venous access was obtained via a 22 gaugeangiocatheter. A dynamic acquisition was then performed during handinjection of gadopentetate dimeglumine (Berlex Laboratories, CedarKnoll, N.J.) 0.2 millimoles/Kg. In 12 patients, the injection was givenas a bolus. The bolus was begun within 5 seconds of starting theacquisition and completed within the first 1 to 2 minutes of the 5minute scan. In the other 40 patients, an injection of the same dose wascarefully timed to be constant and continuous over the entire period ofimaging beginning within 5 seconds of commencing the acquisition andending 20 seconds before the end of the acquisition. In all patients, a5 cc normal saline chaser was given to ensure injection of the entiregadopentetate dimeglumine dose.

For comparison purposes, 16 of these patients were imaged with anidentical acquisition after the dynamic infusion without altering theimaging or prescan parameters. Also, for comparison, axial 2D andmultiple overlapping 3D (MOTSA) time-of-flight images were acquiredprior to the gadolinium injection. Inferior pre-saturation pulses wereused with the time-of-flight sequences to suppress venous in-flow.

Signal intensity was measured in all patients in the aorta, IVC andbackground tissues (fat and skeletal muscle) for at least 3 regions ofinterest per measurement for all sequences. The signal's standarddeviation within the aorta was recorded as noise.

Images obtained dynamically, during steady infusion of gadopentetatedimeglumine, showed sufficient arterial enhancement to clearly definethe aorta and branch vessel anatomy while the IVC and iliac veinsremained indistinguishable from the background tissues. The portal veinis visible but is not as bright as the aorta. Images obtainednon-dynamically, after the injection was completed, or with a dynamicbolus injection demonstrated comparable enhancement of both arteries andveins.

The observation of significant, preferential arterial enhancement with acontinuous dynamic contrast infusion was confirmed by region of interestanalysis (see TABLE 5 and FIG. 9). The ratio of aorta to IVC signalintensity for the 5 minute infusion, 2.0±0.5, was significantly higherthan for non-dynamic imaging 1.1±0.1 (p<0.001) or for the dynamic bolus1.2±0.2 (p<0.001). Even better differentiation between the aorta and IVCwas obtained by injecting the same dose of gadopentetate dimegluminemore quickly over a 3:18 minute acquisition. Although this aorta-to-IVCsignal intensity ratio was not as favorable as for 2D time-of-flight orMOTSA imaging, it was adequate in all cases for clearly distinguishingthe aorta and abdominal aorta branch vessels from the IVC and iliacveins.

Dynamic contrast enhanced 3D imaging had no saturation, pulsatility ormisregistration artifacts. Even in aneurysms, which tend to havestagnant and/or turbulent flow, there was no loss of signal. Bycomparison, every 2D time-of-flight study had pulsatility artifacts andsome had misregistration and/or in-plane saturation artifacts. The MOTSAimages had no pulsatility or misregistration artifacts but every MOTSAstudy showed some degree of arterial saturation and they wereparticularly degraded in aneurysmal segments.

Administering gadopentetate dimeglumine dynamically as a steady,continuous, infusion for the entire period of a 3D FT acquisition, at adose of 0.2 millimoles/Kg, gives sufficient preferential arterialenhancement to visualize arteries distinctly from veins and backgroundtissues regardless of the magnitude or direction of flow. The importanceof injecting dynamically and continuously during the entire scan isillustrated by the absence of significant preferential enhancement whenthe contrast is administered non-dynamically or as a dynamic bolus.Images obtained at a lower dose, 0.1 millimole/Kg, were not useful.

Since dynamic gadolinium enhanced MRA does not depend upon the in-flowof unsaturated spins, it eliminates some of the saturation problems thatcomplicate routine time-of-flight imaging. The imaging volume can beoriented in any plane for optimal coverage of the vessels of interestwithout concern for saturation. In these patients, in-plane, coronalimaging of the aorta-iliac system reduced the image acquisition time by5 to 20 fold over 2D time-of-flight and MOTSA imaging and had superiorresolution and superior aorta signal-to-noise ratios.

A 3D FT acquisition was used in this example partly because of itsintrinsically high spatial resolution and high signal-to-noise and alsobecause its main limitation, arterial saturation, is eliminated by thegadolinium. The TE was chosen to be as short as possible at a valuewhere fat and water protons are out of phase. A short TE helps tominimize motion related phase artifacts. Having fat and water out ofphase provides an element of fat suppression which improvesartery-to-background contrast since fat is the brightest backgroundtissue.

EXAMPLE 3

MRA image data for a patient presenting with an abdominal aorticaneurysm was acquired as described in Example 1. MRA images are shown inFIGS. 10A and 10B.

The MRA of FIG. 10A depicts the aneurysmal aorta and aneurysmal commoniliac arteries as well as severe stenoses of the right external iliac(curved arrow) and inferior mesenteric (straight arrow) arteries and amild stenosis of the left common iliac artery. The internal iliacarteries are excluded because of their posterior course. FIG. 10Billustrates a digital subtraction angiogram which confirms the findingsin FIG. 10A as discussed immediately above.

EXAMPLE 4

A pump (as illustrated in FIG. 5A) was loaded with a 50 cc syringecontaining 42 cc of gadodiamide. A 23 gauge butterfly was attached tothe end of the syringe with its standard luer-lock connector and pluggedinto a side port of the patient's intravenous (IV) line within a fewfeet of the IV skin entry site. The pump was located approximately 15 cmor more away from the imaged volume.

Usually the IV site was in the forearm or antecubital fossa. A plasticKelly clamp on the butterfly tubing prevented premature gadoliniuminfusion. The gadolinium infusion was begun simultaneous with beginningthe image acquisition by releasing the clamp on the butterfly tubing.This combination of 6 pounds spring force and a ⅝ inch, 23 gaugebutterfly needle gave an infusion rate of 18 cc/minute which wasslightly reduced by the additional resistance of the IV tubing andangiocatheter. For the 42 cc volume of gadolinium, the calculatedinfusion time was 2:20 minutes. This was shortened by manuallyincreasing the rate of injection during the middle of the acquisitionsuch that the maximum arterial concentration occurred during acquisitionof the center of k-space.

The pump infusion finished with one minute of scan time remaining.Residual gadolinium within the IV tubing (about 4 cc) was flushedthrough with saline to ensure delivery of the entire dose.

The procedure of EXAMPLE 4 produced excellent quality MRA images ofarteries without the confounding effects of excessive venousenhancement.

EXAMPLE 5

By way of overview, anatomic data defined by magnetic resonance imaging,including abdominal aortic aneurysm size and character as well as thestatus of the celiac, mesenteric, renal and iliac arteries, wereexamined in 43 patients. Five magnetic resonance sequences used inexamining these patients. The five magnetic resonance sequences wereobtained in about an hour-long exam optimized for aortoiliac, splanchnicand renal artery imaging at 1.5 Tesla in a body coil. Four of thesequences were performed during or following infusion of gadolinium toimprove image quality.

Imaging was performed on a 1.5 Tesla Magnet (GE Medical Systems, Signa,Milwaukee, Wis.) using the body coil. The imaging sequences includedSagittal T1 (9:36 minutes), Coronal 3D spoiled gradient echo duringinfusion of 42 or 63 ml gadolinium chelate (3:20 minutes), Sagittal 2Dtime-of-flight (4 minutes), Axial 2D time-of-flight (10 minutes), andAxial 3D phase contrast (13:07 minutes) images. Each sequence wasperformed using the GE Signa Magnet, 1.5 Tesla with 5.3 software. Theimaging parameters, details regarding the gadolinium infusion rate andtiming, and methods of image reconstruction are described in more detailbelow.

Magnetic resonance images were independently analyzed by two vascularradiologists blinded to the findings at angiography, surgery, andcomputed tomography. Any disagreements in interpretation were resolvedby consensus. Aneurysms were classified as suprarenal (aneurysmal abovethe renal arteries), pararenal (aneurysm at level of renal arteries butnot higher), juxtarenal (origin of aneurysm at or within 1 cm belowrenal arteries) or infrarenal (origin of aneurysm more than 1 cm belowrenal arteries). (See TABLE 6). The distal extent was defined as thefirst point inferior to the aneurysm that was near-normal caliber. Themaximum aneurysm diameter was measured electronically on the MR computermonitor from its outer-to-outer wall margins. Thrombus, when present,was noted. The celiac, proximal superior mesenteric, renal, commoniliac, external iliac, and internal iliac arteries were graded asnormal, mildly diseased (less than 50%), moderately stenotic (50-75%),severely stenotic (greater than 75%) or occluded.

Magnetic resonance images were also evaluated for evidence of aorticdissection, inflammatory changes and aortic rupture. Aortic dissectionmay be defined as an aorta having an intimal flap or medial separation.Inflammatory aneurysm may be defined as having surrounding enhancingtissue. Ruptured aneurysm may be defined as having an aortic muraldefect and a retroperitoneal collection with magnetic resonance featuresof hemorrhage.

The imaging parameter details are described below in a form compatiblewith the GE Signa Magnet, 1.5 Tesla with 5.3 software. Those parameters,however, may be converted or extrapolated for use with other imagingsystems; and, as a result, they are exemplary in nature.

An initial sagittal T1-weighted spin echo localizer was landmarked justbelow the xyphoid and obtained using the following parameters: TR=333msec, TE=25 msec, bandwidth=16 kHz, slice thickness=8 mm (performed as atriple interleave with no gap), respiratory compensation, matrix=256 by128 pixels with frequency encoding superior to inferior, a 40-48 cmfield of view and 2 NEX. Image acquisition time was 9:35 minutes.

A first gadolinium-enhanced acquisition was a coronal 3D spoiledgradient echo sequence centered on the abdominal aorta and obtained withthe following parameters: TR=24 msec, TE=6.9 msec, flip angle=40degrees, bandwidth=16 kHz, 28 slices with 2.5 to 2.8 mm slice thickness,matrix=256 by 256 pixels, frequency encoding superior to inferior, firstorder gradient moment nulling (flow compensation), field-of-view=36 cm,1 NEX. No saturation pulses were employed; the total image acquisitiontime was 3:20 minutes.

The coronal volume was positioned with the top edge at the diaphragmjust below the heart and the front edge anterior to the pre-aortic leftrenal vein where it passed under the superior mesenteric artery andanterior to the common femoral arteries at the level of the femoralheads. If the posterior edge of the volume did not reach back into therenal parenchyma bilaterally, the slices were made thicker up to amaximum thickness of 2.8 mm. In most cases, this 28 slice coronal volumewas too thin to image the entire aneurysm; accordingly the anteriormargin of the aneurysm was deliberately excluded on this sequence.

Gadolinium was infused during the acquisition in order to preferentiallyenhance arteries more than veins. The same volume, 42 ml (two vials, 21mMol), Gadodiamide (Omniscan; Sanofi Winthrop Pharmaceuticals, New York,N.Y.), Gadoteridol (ProHance; Squibb Diagnostics, Princeton, N.J.) orGadopentetate Dimeglumine (Magnevist; Berlex Laboratories, Wayne, N.J.)was used in every patient under 95 Kg (210 pounds). Patients weighinggreater than 95 Kg were given three vials (63 ml) of gadolinium. Thegadolinium infusion was begun simultaneously with image acquisitionusing an MR compatible infusion pump (Redington Medical Technologies,Inc. East Walpole, Mass.) The infusion was completed 60 seconds prior toscan termination including a 10 to 20 ml saline flush. This saline flushwas given to ensure delivery of the entire dose of contrast. Specialcare was taken to maintain a high infusion rate during the middle of theacquisition when the center of k-space was acquired.

Immediately following the dynamic gadolinium acquisition, 6 to 8contiguous, sagittal 2D time-of-flight, spoiled, gradient echo imageswere acquired, centered on the visceral arteries with the followingparameters: TR=33, TE=minimum (7 msec), flip angle=45 degrees,bandwidth=16 kHz, slice thickness=6 cm, first order gradient momentnulling (flow compensation), matrix=256 by 192, frequency encodingsuperior-to-inferior, 36 cm field-of-view, 1 NEX. Each sagittal imagewas obtained during suspended respiration (7 seconds per breath hold).Immediately following these sagittal images, axial 2D time-of-flightgradient echo images were obtained in a similar fashion with thefollowing parameters: TR=22 msec, TE=minimum full (12 msec), flipangle=60 degrees, bandwidth=16 kHz, slice thickness=8 mm with a 5 mminterslice gap, matrix=256 by 256, 28 to 32 cm field-of-view, firstorder gradient moment nulling (flow compensation), and no phase wrap.The axial images covered from above the celiac trunk to below the AAA.If the iliac arteries were aneurysmal, the axial 2D time-of-flightimages were extended down into the pelvis. The acquisition was performedeither with 2 averages (NEX) and suspended respiration or with 4averages and phase reordering with respiration (respiratorycompensation).

Following the time-of-flight images (sagittal and axial 2Dtime-of-flight images), an axial 3D phase contrast volume was acquiredcentered on the renal arteries with the following parameters: TR=24msec, TE=7.7 msec, flip angle=45 degrees, bandwidth=16 kHz,field-of-view=32 cm, 28 slices with 2.5 mm slice thickness, flowcompensation, no phase wrap, matrix=256 by 128, frequency encodingright-left, 32 cm field-of-view, 2 NEX with velocity encoding in alldirections at 30 cm/sec. The image acquisition time was 13:07 minutes.Images were reconstructed with the phase difference method illustratingmaximum velocity in all flow directions as well as right-to-left flow toevaluate the retrocaval course of the right renal artery. In patientssuspected of having very slow renal artery flow, such as patients with aserum creatinine greater than 3 mg/dl, the velocity encoding was reducedto 20 cm/sec.

Images were reconstructed by a vascular radiologist using a computerworkstation (GE Medical Systems, Milwaukee, Wis.) Subvolume maximumintensity projections and single voxel thick reformations were madethrough the origins of each of the major aortic branch vessels. Thesubvolume maximum intensity projections were made by reviewing the rawdata images to identify the minimum number of images required todemonstrate the renal arteries and then collapsing these into a singlecoronal image. This was similarly performed for the aorto-iliac system.A sagittal subvolume maximum intensity projection was performed centeredon the celiac and superior mesenteric arteries for both the dynamicgadolinium-enhanced coronal sequence and for the sagittal 2Dtime-of-flight sequence.

EXAMPLE 6

Twenty-five patients were imaged with a shortened 3D spoiled gradientecho acquisition that could be performed during suspension ofrespiration. To shorten the acquisition time to under 1 minute, the TRwas reduced to 14 msec and the TE was reduced to 2.6 msec. A 28 slice 3Dvolume with a 256 by 128 matrix required a 58 second breath-hold and a12 slice volume required a 29 second breath-hold.

Gadolinium was infused intravenously as a 30 second bolus beginningapproximately 40 to 50 seconds before the middle of the imageacquisition. In this way, the arterial gadolinium concentration wasexpected to be maximum during the middle of the acquisition when datarepresentative of the center of k-space was acquired.

It should be noted that for short scans (i.e., less than 1 to 2 minutes)one manner of calculating a scan time delay (i.e., a delay between thebeginning of imaging and the beginning of infusion) more accurately isto employ the following relationship:

Scan Time Delay=Estimated circulation time+(infusion time/2)−(imagingtime/2)

The estimated circulation time is the time required for contrast totravel from the site of injection/infusion to the artery of interest;the infusion time is the time duration of the contrast infusion; and theimaging time is the time duration of the image acquisition. Therelationship defined above assumes that the data representative of thecenter of k-space is acquired in the middle of the image acquisition. Inthose instances where data corresponding to the center of k-space iscollected at a time other than during the middle of the acquisition, therelationship may be adjusted accordingly.

In all patients who were able to cooperate with breath-holding, therenal arteries were well seen all the way to the renal hilum. In twopatients who could not cooperate with breath-holding there wasdegradation (blurring) of the distal renal artery making it moredifficult to evaluate.

EXAMPLE 7

Patients: Sixty-three patients underwent magnetic resonance angiography(“MRA”) of the abdominal aorta including renal and mesenteric arteriesusing dynamic gadolinium enhancement during breath holding. The patientsincluded 28 males and 35 females, ranging in age from 22 to 87 years.Primary indications for imaging included suspected renovascularhypertension (n=25), suspected mesenteric ischemia (n=13), abdominalaortic aneurysm (n=5), renal transplant donor (n=5), peripheral vasculardisease (n=4), renal mass (n=2), renal failure (n=2), aortitis (n=1) andto evaluate vascular anatomy post aortic reconstruction (n=6). Ninepatients had renal insufficiency with serum creatinines ranging from 1.6to 10.4 mg/dl (mean=3.2 mg/dl).

Imaging Technique: All patients were imaged in a 1.5 Tesla superconducting magnet (Signa with 5.3 or 5.4 operating system software,General Electric Medical Systems, Milwaukee, Wis.) using the body coil.Three sequences were performed as follows:

(1) An initial sagittal T1-weighted spin echo localizer was obtainedcentered just below the xyphoid using the following parameters: TR=385msec, TE=17 msec, bandwidth=16 kHz, slice thickness=8 mm (performed asan interleave with no gap), respiratory compensation, matrix=256×256pixels with frequency encoding superior to inferior, a 40-48 cm field ofview, and two averages (NEX). Image acquisition time was 7 minutes 11seconds.

(2) The initial sagittal T1-weighted spin echo localizer sequence wasfollowed by a coronal 2D time-of-flight spoiled gradient echo sequencewith the following parameters: TR=20 msec, TE=6.9 msec, flip angle=30degrees, bandwidth=16 kHz, field of view=32 cm, slice thickness=2.9 mmand first order gradient moment nulling. With a 256×128 matrix and twoaverages it was possible to acquire three sequential images in a 16second breath hold. Images were obtained from just anterior to the leftrenal vein back to the renal hila, with a total of 14 to 24 images.

(3) A gadolinium-enhanced, 3D, spoiled gradient echo MRA sequence wasperformed during breath holding following the coronal 2D time-of-flightspoiled gradient echo sequence. For examinations focusing on the renalarteries (48 patients), this sequence was performed in the coronal planegraphically prescribed on a midline sagittal T1-weighted image (sequence#1). The coronal 2D time-of-flight images of sequence #2 were used as aguide for determining the anterior and posterior extent required tocover the renal arteries. For exams focusing on the celiac trunk andsuperior mesenteric artery (15 patients), this sequence was performed inthe sagittal plane graphically prescribed on a coronal 2D time-of-flightimage of sequence #2.

Breath Holding: Since most patients can suspend breathing for a maximumof 30 to 60 seconds, the parameters were adjusted to keep theacquisition time to under 1 minute. The TR was reduced to 14.1 msec, andthe TE was reduced to 2.6 msec by using an asymmetric echo andeliminating the gradient moment nulling (flow compensation). With a256×128 matrix, it was possible to acquire a 12 slice volume in 29seconds or a 28 slice volume in 58 seconds using a 16 kHz bandwidth. Theactual number of slices was 16 or 32 but two slices at each end of thevolume were discarded due to aliasing from phase encoding in the sliceselect direction. Frequency encoding was superior-to-inferior.

Initially, it was thought that most patients would have difficultysuspending breathing for longer than 30 seconds. Accordingly, the firstpatients studied were imaged with the 12 slice 3D volume and a 256×128matrix that required only 29 seconds. The slice thickness had to be atleast 3-3.5 mm in order to cover renal arteries from their origins tothe renal hila or to adequately cover the celiac and SMA.

When it became apparent that many patients could suspend respiration forlonger than 29 seconds, the image acquisition time was increased to 43seconds (12 slices with a 256×192 matrix) and subsequently to 58 seconds(28 slices with a 256×128 matrix). For the 28 slice acquisitions, theslice thickness could be reduced to 2 mm except for the patients withabdominal aortic aneurysms who required 2.5 to 3 mm thick slices. Atotal of seven patients (eight exams) were imaged in 29 seconds, 11 (12exams) were imaged in 43 seconds and 45 (46 exams) were imaged in 58seconds.

All patients were instructed to take four deep breaths in rapidsuccession (hyperventilation) prior to breath holding. Oxygen wasadministered at a rate of 2 to 4 L/min by nasal canulae to patients whowere likely to have difficulty suspending respiration. These patientswere also given the option to take a single quick breath toward the endof the scan if breath holding became intolerable.

Appendage Cushions: To maintain high spatial resolution with the reducednumber of phase encoding steps, the field of view was reduced to 26-32cm. For coronal acquisitions, this small field of view lead to aliasingin the right-left direction. Appendage cushions resolved thedifficulties presented by aliasing. The appendage cushions (about 8 cmthick of non-magnetic, low density, “spongy” material, e.g., foam) werepositioned along each side of the torso to elevate the arms out of theimage plane (FIG. 13). In addition to reducing the aliasing presented bya small field of view, the appendage cushions elevated the arms whichenhanced the venous return for rapid clearing of gadolinium from veins.

Flip Angle Selection: To determine a suitable flip angle, the arterialblood signal intensity was calculated for a range of flip angles and T1relaxation times. The calculated arterial blood T1 is 28 msec for adynamic infusion of 40 ml gadopentetate dimeglumine over 30 seconds (40mMol/min) into a cardiac output of 5 liters/min (8 mMolar). However, theactual arterial blood T1 occurring during the center of k-space islikely to be substantially longer than 28 msec due to the imperfecttiming of the gadolinium bolus in relation to the mapping of k-space.Additional factors contributing to a longer T1 include stagnation ofgadolinium in the veins beyond 30 seconds and the failure to completethe injection and flush in 30 seconds. Based on these calculations andconsiderations, a flip angle of 45 degrees was selected to maximizearterial contrast for an estimated arterial blood T1 of approximately 50msec.

Timing of the Gadolinium Bolus for Breath Hold Gd MRA: All patientsreceived 42 ml (two vials) of gadolinium contrast (gadodiamide, Nycomed,New York, N.Y.; gadoteridol, Bracco, Princeton, N.J.; or gadopentetatedimeglumine Berlex Laboratories, Wayne, N.J.) regardless of weightalthough the dose per weight was recorded. In preparation for theinjection, the intravenous line was filled with gadolinium using 5-8 mldepending on the length of IV tubing. This process of initially fillingthe intravenous tubing provided a sense of flow resistance and thusaided gauging how much force was required for the injection. Thegadolinium was injected by hand over 25 to 30 seconds and immediatelyfollowed with 20-50 ml normal saline to complete delivery of the entiregadolinium dose and to flush the veins of gadolinium. To help minimizeany delay in performing the saline flush, intravenous tubing with twoside ports was used, one for gadolinium and one for the saline flush(FIG. 13). When gadopentetate dimeglumine was used, its viscosity wasreduced by placing it in a 37° C. incubator 2 to 3 hours prior toinjection. This lowered its viscosity to a level comparable togadodiamide and gadoteridol, making it possible to rapidly infusethrough a 20 or 22 gauge angiocatheter.

Since the 3D spoiled gradient echo sequences on Signa systems fill ink-space linearly, from bottom to top, the central half of k-space wasacquired during the middle half of the acquisition. It was the centralportion of k-space that had the low spatial frequency information whichdominated image contrast. In order to make arteries bright, thegadolinium bolus was timed for the arterial phase to occur duringacquisition of this central portion of k-space.

The time required for the intravenously administered gadolinium to reachthe abdominal aorta has substantial variation, which may range from 10to 50 seconds for injections into an antecubital vein. This circulationtime is generally longer in older patients and in patients with poorcardiac output. It is shorter in young, hypertensive individuals. Foreach patient, the circulation time (peak) was estimated based on age andclinical status. As indicated in Example 6, a “scan delay” betweenbeginning the gadolinium infusion and beginning the 3D acquisition maybe calculated from the following estimate of the circulation time of thecontrast agent:

Scan Delay=Estimated Circulation Time+(Infusion Time/2)−(Imaging Time/2)

Using this approach, the middle of the 30 second infusion was expectedto reach the arteries during the midpoint of the acquisition, therebyproviding maximum arterial gadolinium concentration in the region ofinterest during acquisition of at least the central half of k-space.

For example, a 25-55 year old hypertensive patient with an estimatedcirculation time of about 15 seconds who could suspend respiration for58 seconds would have a delay between beginning the infusion andbeginning scanning of about 1 second. Older patients with cardiacdisease or an aortic aneurysm with an estimated circulation time of 25to 35 seconds would have a delay between beginning the infusion andbeginning scanning of 10 to 20 seconds for the 58 second breath hold or25 to 35 seconds for the 29 second breath hold. If the intravenous linewas in the hand or distal forearm, the scan delay was made a few secondslonger and a larger saline flush was used.

Image Reconstruction: Images were reconstructed by a vascularradiologist using a computer workstation (General Electric MedicalSystems, Milwaukee, Wis.). Subvolume maximum intensity projections(MIPs) and single voxel thick reformations were made through the originsof each renal artery, the celiac trunk and the superior mesentericartery. Reformations were performed in flat 2D planes and occasionallyin curved planes as well. The subvolume MIPs were made by reviewing theraw data images to identify the minimum number of images required todemonstrate the renal arteries and then collapsing these into a singlecoronal image. MIPs were also made in axial, sagittal, and obliqueplanes by orienting the plane of reformation for optimal alignment tothe artery-of-interest and then increasing the slab thickness toencompass the entire artery.

Image Analysis: In order to evaluate image quality, the signal-to-noiseratio (SNR) and artery-to-adjacent tissue contrast-to-noise ratio (CNR)were measured in the aorta in every patient and in the proximal anddistal renal artery in patients imaged in the coronal plane. Thesemeasurements were also obtained in 104 consecutive patients imaged withthe previously described coronal 3D technique performed without breathholding. The standard measurement of the intrinsic image noise made froma region outside the patient was not possible because of the small fieldof view. Assuming that the arterial blood signal should be uniform overthe vascular region of interest, any variation in arterial blood signalwas considered to represent a combination of both the intrinsic imagenoise and the additional image noise from respiratory and other motionartifacts. Accordingly, the standard deviation of the arterial bloodsignal was considered “total noise” in that vascular segment forpurposes of calculating the SNR. The signal-to-total-noise ratio isdenoted as SNR* to distinguish it from the more conventional SNRmeasurement. Similarly, the contrast-to-total-noise ratio is denoted asCNR*. Degradation of images from blurring of the abdominal organs wasalso noted.

MRA was correlated with angiography by comparing the reports generatedprospectively for each of the MR studies with the conventionalangiography reports. All MRA exams were interpreted by a single vascularradiologist without knowledge of the angiography reports. Renal, celiacand mesenteric arteries were graded in these reports as normal, mildlystenotic (<50% stenosis), moderately stenotic (50-75% stenosis),severely stenotic (>75% stenosis) occluded or not visualized. The MRAwas considered to “agree” with conventional angiography if the celiac,SMA and renal arteries were graded in MR reports the same as inangiography reports. The number of accessory renal arteries and renalartery branch vessels (including both hilar and prehilar branches)visualized by MRA for each kidney were also determined.

Statistical Analysis: The differences in SNR* and CNR* measurements andin the mean number of branch vessels seen between the free breathing andbreath held techniques were compared using Student's t-test. Differencesin the proportions of exams with blurring and the proportions of kidneysfor which renal artery branches were seen between the free breathing andbreath-held techniques were compared using the Chi square test.

Results: In all patients, the abdominal aorta and the origins of theceliac, superior mesenteric artery and renal arteries were visualized onbreath held 3D gadolinium MRA.

Image Quality: There was 25-50% greater SNR* and 60-120% greater CNR*with breath holding compared to free breathing (p<0.01) as shown inTable 7. The breath holding technique also identified 71% more renalartery branches (p<0.001).

Fourteen of 66 breath held exams (21%) had blurring of the abdominalorgans with the breath held technique compared to 108 of 120 exams (90%)during free breathing (p<0.001). The blurring of the abdominal organsindicate motion during the data acquisition. This occurred in 12 of 46(26%), 58 second breath held exams, two of 12 (17%) 43 second exams, andnone of the 29 second exams.

One patient had both a breath held exam as well as an exam performedduring free breathing. In this patient, the renal artery anatomy wasbetter defined on the breath-held exam.

All three breath held image times, 29, 43, and 58 seconds, hadcomparable arterial SNR* and CNR*. Axial, sagittal, and obliquereformations, however, had noticeably higher resolution with the 28slice volume compared to the 12 slice volumes, presumably because of thesmaller and more isotropic voxels.

Angiographic Correlation: Lateral aortograms were available to evaluatethe celiac axis and proximal superior mesenteric artery in 8 of the 19patients with angiographic correlation. Frontal and oblique aortogramswere available in 18 patients with a total of 46 renal arteries. Twoceliac stenoses, 1 celiac occlusion, 2 SMA stenoses, 3 renal arterystenoses and 1 renal artery occlusion were identified by MR andcorrectly graded. There were 3 discrepancies including a mild celiacstenosis graded as moderate by MR, a moderate renal artery stenosisgraded as normal by MR and a normal renal artery graded as moderatelystenotic by MR. In addition, in one patient with a liver transplant,thrombocytosis, and a history of Budd Chiari syndrome who had been onlong term anticoagulation, MR graded the left renal artery as severelystenotic. At angiography, the left renal artery was found to be occludedbut the fresh thrombus could easily be crossed with a wire andsuccessful balloon angioplasty was performed. We felt that most likelythe renal artery progressed from severe stenosis to occlusion betweenthe MR and conventional arteriography due to withdrawal ofanticoagulation in preparation for angiography. Overall, the 3Dgadolinium MRA studies were in agreement with conventional angiographyin 15 of these 19 (79%) patients.

Ten of eleven (91%) accessory renal arteries demonstrated at angiographywere also demonstrated on MRA. The one error occurred in a patient whocould not hold his breath for the entire 58 seconds. In one patient,angiography failed to recognize a tiny upper polar artery because ofsuperposition of SMA branches. It was identified only in retrospectfollowing analysis of the 3D gadolinium MRA.

Associated Lesions: Six patients had abdominal aortic aneurysms.Additional pulse sequences were required to image the anterior extent ofthe aneurysms and to evaluate mural thrombus. Renal or splanchnic arteryreconstructions were imaged postoperatively in 6 patients includingthree with aortorenal bypass grafts. None of these studies were impairedby metallic clip artifacts. One of these patients exhibited a smallrenal infarct following a renal artery endarterectomy. A type III aorticdissection involving the abdominal aorta was seen in one case andconfirmed by angiography. MRA demonstrated the dissection and correctlycharacterized the relationship of the true lumen to the celiac, superiormesenteric and renal artery origins. Enhancing renal masses wereidentified in two patients that were confirmed following nephrectomy tobe renal cell carcinoma. However, the technique was not used to screenfor renal masses because the posterior portions of the kidneys wereexcluded.

Adverse Reactions: All patients tolerated the procedure well. There wereno allergic type reactions. No patient experienced nausea. One patientdescribed a transient metallic taste immediately after a 42 ml infusionof gadodiamide. Periexamination serum creatinine levels were availablein 15 patients. In these patients, the mean serum creatinine level was1.8±2.4 mg/dl on the day of or the day before the MRA exam and 1.8±2.6mg/dl the next day. No gadolinium contrast extravasations occurred inany of the patients despite many of the intravenous lines being locatedin hand or distal forearm veins.

Comments: In this EXAMPLE, respiratory motion was suppressed oreliminated by acquiring images in a single breath. The reduction inimaging time required for breath holding would normally be expected todiminish image quality. Data in this series of 63 patients, however,demonstrate that the elimination of respiratory motion and the fastergadolinium infusion resulted in an improvement in image quality.

These fast, breath-held 3D images improved in several ways upon the 3Dgadolinium-enhanced techniques performed without breath holding. First,the aorta and renal arteries had higher SNR* and CNR*. Second, thedistal renal arteries and renal artery branches were seen in a largerproportion of patients. Third, accessory renal arteries were correctlyidentified with greater frequency. Fourth, fewer patients had blurringof the abdominal organs. Fifth, visualization of differentialenhancement between normal and ischemic kidneys allowed assessment ofthe hemodynamic significance of stenoses.

The imaging technique of this EXAMPLE provided satisfactory resultsnotwithstanding the fact that circulation time of the contrast agent wasestimated based upon clinical impression. An more accurate circulationtime may be obtained by measuring the actual circulation time in advanceof contrast agent injection by using decholin, saccharin, magnesiumsulfate, or a test bolus of gadolinium.

The imaging technique of this Example, however, may be implemented inconjunction with the detection-imaging technique of the presentinvention which provides precise synchronization between collection ofimage data which is representative of the center of k-space and thearterial phase of contrast enhancement.

Another aspect of this Example included the patient's ability to breathhold. Many of the patients were able to hold their breath for 29, 43 or58 seconds. In 14 patients, however, image “blurring” indicated thatthey either did not sustain the breath hold for the entire scan or theywere moving their diaphragm despite breath holding. Most of the blurringoccurred in the 58 second studies suggesting that the problem wassustaining the long breath hold.

The blurring may be alleviated or minimized with the use of fasterscanners which acquire the necessary 3D volume in less time. It may alsobe improved or corrected by using a wider bandwidth. Increasing thebandwidth from 16 to 32 kHz reduces the 28 slice scan time from 58 to 43seconds on our equipment. Such a change in the frequency or bandwidthmay result in a decrease in SNR.

A 45 degree flip angle was used in this study, anticipating that errorsin timing the infusion would result in a lower than expected arterialblood gadolinium concentration during the acquisition of the centralportion of k-space. Should this timing be optimal, an improvement in theimage contrast may be obtained by increasing the flip angle. When thearterial T1 is reduced to less than 50 msec, flip angles larger than 45degrees will extract more signal from the arterial blood and, at thesame time, achieve greater background suppression. In a preferredembodiment, a flip angle of about 60 degrees may be optimal when 42 mlof gadolinium is injected over 30 seconds, timed to perfectly coincidewith the center of k-space.

Various preferred embodiments of the present invention have beendescribed. It is understood, however, that changes, modifications andpermutations can be made without departing from the true scope andspirit of the present invention as defined by the following claims,which are to be interpreted in view of the foregoing.

TABLE 1 Infusion Rates of Gadolinium Chelates at 24° C. Gd-DTPAGadoteridol Gadodiamide Viscosity @ 20° C. [cP]* 4.9 2.0 2.0 InfusionRate Flow Restrictor Size Gd-DTPA Gadoteridol Gadodiamide Needles BD ®18 g 1.5″ 100  126  120  Terumo ® 20 g 1.5″ 44 66 64 Terumo ® 21 g 1.5″27 47 44 Terumo ® 22 g 1.5″ 15 29 23 Terumo ® 23 g 1″ <4 <4 <4Butterflies ABBOTT ® 21 g .75″ 21 37 36 ABBOTT ® 23 g .75″  8 19 18ABBOTT ® 25 g .375″ <4  8   7.3 Orifice 0.010″ 21 25 25 *Values providedby manufacturer (Nycomed)

TABLE 2 Aorta/IVC Signal Intensity Ratios for Dynamic 3D Imaging PatientPrimary Heart Signal Intensity During Injection # - sex Age IndicationDisease Creatinine Aorta IVC ratio** p value 1-m 83 AAA yes* 2   7.9 ±1.0  3.9 ± 0.6 2.0 <.0001 2-f 73 hypertension yes*  .8 11 ± 1.0 8.2 ±1.3 1.4  .0002 3-m 73 claudication yes 2.2 10 ± 2.0 3.7 ± 0.5 2.8  .00034-f 67 hypertension no  .9 10 ± 0.4 5.1 ± 0.6 2.0 <.0001 5-f 70hypertension yes* 3   8.9 ± 0.9  4.5 ± 0.4 2.0 <.0001 6-m 67 renalfailure yes 6   11 ± 0.5 4.9 ± 0.4 2.2 <.0001 7-f 80 AAA yes 1.8 10 ±0.4 5.9 ± 0.5 1.8 <.0001 8-f 76 renal failure yes* 3.6 9.1 ± 0.6  5.0 ±0.6 1.8 <.0001 9-m 68 AAA no 1   11 ± 0.5 7.2 ± 0.3 1.4 <.0001 10-m 70claudication yes 1.2 11 ± 0.5 5.4 ± 0.3 2.0 <.0001 11-m 74 hypertensionno 1   8.9 ± 0.3  6.0 ± 0.8 1.5 <.0001 12-m 80 hypertension yes* 3.2 10± 0.4 3.8 ± 0.9 2.6 <.0001 13-m 74 AAA yes 4   9.8 ± 1.0  3.7 ± 0.8 2.6<.0001 14-f 67 AAA no 1   10 ± 0.3 5.9 ± 0.6 1.8 <.0001 15-m 67hypertension no 1.5 11 ± 0.9 4.6 ± 0.9 2.4 <.0001 16-f 71 claudicationyes* 6   11 ± 1.3 3.1 ± 0.6 3.5 <.0001 AVERAGE 10 ± 0.9 5.1 ± 1.4 2.0<.0001 *cardiac disease with history of CHF **Aorta/IVC signal intensityratio

TABLE 3 Average Signal-To-Noise Ratios During and Post GadopentetateDimeglumine Injection Dynamic Post Ratio Injection InjectionDynamic/Post ARTERIES Aorta  10 ± 0.9  10 ± 1.4 1.0  Iliac Artery 9.8 ±1.3  10 ± 1.3 .98 Renal Artery 9.7 ± 1.9  10 ± 2.5 .99 Celiac & SMA  10± 1.7  11 ± 1.8 .91 VEINS IVC 5.1 ± 1.4   9.5 ± 1.3** .54 Iliac Vein 4.7± 1.6*  9.2 ± 1.3** .51 Renal Vein 6.2 ± 1.8*  9.1 ± 1.9** .68 HepaticVein 7.5 ± 2.1*  8.3 ± 1.0** .90 Portal Vein 8.3 ± 1.6*  9.0 ± 3.3** .92BACKGROUND Kidney 7.3 ± 1.0 8.3 ± 1.0 .88 Liver 5.3 ± 0.6 5.8 ± 1.8 .91Spleen 5.9 ± 2.3 6.3 ± 2.3 1.1  Fat 4.3 ± 0.7 4.0 ± 0.8 1.1  Muscle 2.4± 0.5 3.2 ± 0.7 .75 *p > 0.01 compared to IVC signal intensity **p >0.01 compared to signal intensity for dynamic injection ***standarddeviation of signal in the space outside the patient

TABLE 4 Effect of Cardiac Disease, Claudication and Aneurysms onAorta/IVC Signal Intensity Ratio No. of Subgroup Patients Aorta/IVC* pvalue Cardiac Disease 12  2.2 ± 0.6 0.08 No Cardiac Disease 4 1.8 ± 0.40.08 Claudication 4 2.6 ± 0.8 0.12 No Claudication 12  2.0 ± 0.4 0.12Aneurysm 7 2.2 ± 0.7 0.32 No Aneurysm 9 2.0 ± 0.5 0.32 *Signal IntensityRatio

TABLE 5 Effect of Injection Method on Aorta Signal-to-Noise andContrast-to-Noise Ratios Contrast Image Voxel Aorta- Aorta- PulseInjection # of time/cm Volume Saturation Pulsatility Aorta Aorta/IVC IVCAorta-fat muscle Sequence Method patients (sec/cm) (mm³) ArtifactsArtifacts SNR SI ratio CNR CNR CNR 2D TOF No gado 11 40  6.0 yes yes 8.2± 2.8 3.7 ± 1   5.8 ± 1.9 5.5 ± 2   6.8 ± 2.4 MOTSA No gado 12 92  4.7yes no 8.9 ± 2.5 2.7 ± 0.9 5.1 ± 1.8 4.9 ± 1.7 6.3 ± 1.9 Gado: 3Dnon-dynamic 16 9 3.1 no no   9 ± 2.0 1.1 ± 0.1 0.6 ± 0.5 5.4 ± 1.5 6.2 ±1.9 Gado: 3D bolus* 12 9 3.1 no no  12 ± 2.4 1.2 ± 0.2 2.7 ± 1.4 7.5 ±1.6 9.1 ± 1.9 Gado: 3D infusion**¹ 20 9 3.1 no no  10 ± 1.2 2.0 ± 0.54.7 ± 1.4 5.4 ± 1.1 7.3 ± 1.1 Gado: 3D infusion**² 20   5.5 3.1 no no 10± 2  2.4 ± 0.8 5.6 ± 1.7 6.8 ± 1.9 8.2 ± 1.7 SNR = signal-to-noise ratioCNR = contrast-to-noise ratio *gadopentetate dimeglumine givendynamically as a bolus within the first 2 minutes of the acquisition.**gadopentetate dimeglumine given dynamically as a constant infusionspread over the entire acquisition. ¹5 minutes ²3 minutes

TABLE 6 Characteristics of Abdominal Aortic Aneurysms Suprarenal 11Pararenal  6 Juxtarenal  6 Infrarenal 20 Mean Diameter (min-max)  5.4(3-8.7) cm Thrombus 35 (81%) Inflammatory AAA  1 (2%) Leaking AAA  1(2%) Retro-Aortic Renal Vein  6 (14%) Accessory Renal Arteries  5 (12%)

TABLE 7 Effect of Breath Holding on Coronal 3D Gadolinium-enhanced MRAFree Breath Breathing Holding p-value # of Patients in coronal plane 10448 # of Exams in coronal plane 120 51 Imaging Time (minutes) 3:260:29-0:58 Mean Contrast Dose (mMol/Kg) 0.31 0.30 # of Kidneys in WhichRenal 84/236 86/95 <0.001 Artery Branches Seen (36%) (91%) Mean # ofRenal Artery 1.4 ± 0.7 2.4 ± 1.0 <0.001 Branches Seen SNR* Aorta 9.5 ±2.8  14 ± 4.6 <0.001 Proximal Renal Artery 2.6 ± 1.6 3.3 ± 2.6 0.02Distal Renal Artery 2.1 ± 2.5 3.1 ± 2.2 0.02 CNR* Aorta 7.0 ± 2.6  11 ±4.1 <0.001 Proximal Renal Artery 1.4 ± 1.3 2.3 ± 2.3  0.002 Distal RenalArtery 1.0 ± 1.6 2.2 ± 2.1 <0.001

What is claimed is:
 1. An apparatus for imaging an artery of a patientusing magnetic resonance imaging and an administered magnetic resonancecontrast agent, comprising, a monitor unit to allow an operator toobserve a change in a concentration of the contrast agent in a region ofinterest; an operator interface to generate an image acquisition signal;and imaging means for collecting image data which is representative ofat least a portion of a center of k-space in response to the imageacquisition signal wherein the operator interface generates the imageacquisition signal in response to an input from the operator after theoperator observes the change in the concentration of contrast agent inthe region of interest.
 2. The apparatus of claim 1 wherein the operatorinterface generates the image acquisition signal in response to an inputfrom the operator after the operator observes an arrival of the contrastagent in the region of interest and wherein the imaging means collectsimage data which is representative of the center of k-spacesubstantially at a beginning of a 3D imaging sequence.
 3. The apparatusof claim 1 wherein the imaging means collects image data which isrepresentative of a central portion of the center of k-space when aconcentration of the contrast agent in the artery is substantiallyhigher than a concentration of the contrast agent in veins adjacent tothe artery.
 4. The apparatus of claim 3 wherein the operator interfacegenerates the image acquisition signal in response to an input from theoperator after the operator observes a beginning of the arterial phaseof contrast agent enhancement in the region of interest.
 5. Theapparatus of claim 4 further including an administration means foradministering the contrast agent at a rate greater than about 1 cc/secand wherein the region of interest includes at least a portion of theartery and wherein the artery is the aorta.
 6. The apparatus of claim 4further including an administration means for administering the contrastagent at a rate greater than about 0.05 millimoles/sec and wherein theregion of interest includes at least a portion of the artery and whereinthe artery is the aorta.
 7. The apparatus of claim 1 wherein the imagingmeans collects a first image data set including image data which isrepresentative of at least a portion of a center of k-space beforeadministering a magnetic resonance contrast agent and collects a secondimage data set including image data which is representative of at leasta portion of a center of k-space in response to the image acquisitionsignal.
 8. The apparatus of claim 7 wherein the imaging means constructsan image of the artery by subtracting at least two images selected froma set of images comprising images of the first image data set and imagesof the second image data set.
 9. An apparatus for imaging an artery of apatient using magnetic resonance imaging and an administered magneticresonance imaging contrast agent, comprising, a monitoring unit to allowan operator to monitor a region of interest and observe the administeredmagnetic resonance contrast agent arriving in the region of interest; animage acquisition signal generator for generating an image acquisitionsignal; imaging means for collecting image data, in response to theimage acquisition signal, which is representative of a substantialportion of a center of k-space; and wherein the monitoring unit allowsthe operator to synchronize the collection of the image data which isrepresentative of a substantial portion of a center of k-space with aconcentration of contrast agent in the artery which is substantially agreater than a concentration of contrast agent in veins adjacent theartery.
 10. The apparatus of claim 9 wherein the imaging means collectsthe image data which is representative of the center of k-spacesubstantially at a beginning of a 3D imaging sequence.
 11. The apparatusof claim 10 wherein the imaging means collects image data which isrepresentative of a periphery of k-space after collecting image datawhich is representative of the center of k-space.
 12. The apparatus ofclaim 9 further including an operator interface for generating an imageacquisition signal in response to an input from the operator wherein theoperator initiates collection of the image data after observing thearrival of the contrast agent in the region of interest.
 13. Theapparatus of claim 12 wherein the imaging means collects the image datawhich is representative of the center of k-space substantially at abeginning of a 3D imaging sequence.
 14. The apparatus of claim 13wherein the imaging means collects image data which is representative ofa periphery of k-space after collecting image data which isrepresentative of the center of k-space.
 15. The apparatus of claim 12wherein the imaging means collects a first image data set includingimage data which is representative of at least a portion of a center ofk-space before administering a magnetic resonance contrast agent andcollects a second image data set including image data which isrepresentative of at least a portion of a center of k-space in responseto the image acquisition signal.
 16. The apparatus of claim 15 whereinthe imaging means constructs an image of the artery by subtracting atleast two images selected from a set of images comprising images of thefirst image data set and images of the second image data set.
 17. Amethod of imaging an artery of a patient using magnetic resonanceimaging and an administered magnetic resonance contrast agent,comprising, monitoring a region of interest to observe a change in aconcentration of the contrast agent in a region of interest; generatingan image acquisition signal; and imaging at least a portion of theartery in response to the image acquisition signal, including collectingimage data which is representative of the center of k-space while aconcentration of contrast agent in the artery is substantially greaterthan a concentration of contrast agent in veins adjacent to the artery.18. The method of claim 17 further including administering the magneticresonance contrast agent to the patient in a bolus type injection andwherein imaging at least a portion of the artery includes collectingimage data of a 3D imaging sequence and collecting image data which isrepresentative of the center of k-space includes collecting the imagedata substantially at a beginning of the 3D imaging sequence.
 19. Themethod of claim 17 wherein generating an image acquisition signalfurther includes generating the image acquisition signal after observingan arrival of the contrast agent in the region of interest.
 20. Themethod of claim 19 wherein collecting image data which is representativeof the center of k-space includes collecting the image data which isrepresentative of the center of k-space substantially at a beginning ofthe 3D imaging sequence.
 21. The method of claim 19 wherein collectingimage data further includes collecting a first image data set includingimage data before administering a magnetic resonance contrast agent andcollecting a second image data set including image data which isrepresentative of the center of k-space in response to the imageacquisition signal.
 22. The method of claim 21 further includingconstructing an image of the artery by subtracting at least two imagesselected from a set of images comprising images of the first image dataset and images of the second image data set.
 23. The method of claim 17wherein generating an image acquisition signal further includesgenerating the image acquisition signal in response to observing abeginning of the arterial phase of contrast enhancement in the region ofinterest.
 24. The method of claim 23 wherein collecting image datafurther includes collecting a first image data set including image databefore administering a magnetic resonance contrast agent and collectinga second image data set including image data which is representative ofthe center of k-space in response to the image acquisition signal. 25.The method of claim 24 further including constructing an image of theartery by subtracting at least two images selected from a set of imagescomprising images of the first image data set and images of the secondimage data set.